Ophthalmologic apparatus

ABSTRACT

An ophthalmologic apparatus of an embodiment includes an examination part, a moving mechanism, an information obtaining part, and a controller. The examination part is configured to include an optical system for optically examining an eye. The moving mechanism is configured to move the optical system. The information obtaining part is configured to obtain information for carrying out position matching of the optical system to the eye. The controller is configured to carry out first control for the moving mechanism based on the information obtained by the information obtaining part to move the optical system, determine whether information optically obtained by the optical system after the first control is appropriate to the examination or not, and when it is determined that this information is not appropriate, carry out second control for the moving mechanism in response to a prescribed trigger to move the optical system.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a Continuation in Part of application Ser. No.14/226,290 filed Mar. 26, 2014, which claims benefit of U.S. ProvisionalApplication No. 61/807,923 filed Apr. 3, 2013, which are incorporatedherein by reference in their entirety.

TECHNICAL FIELD

The present invention relates to an ophthalmologic apparatus thatperforms optical examination of an eye.

BACKGROUND TECHNOLOGY

Types of ophthalmologic apparatuses include ophthalmologic imagingapparatuses for obtaining images of an eye and ophthalmologic measuringapparatuses for measuring characteristics of an eye.

Examples of ophthalmologic imaging apparatuses include an opticalcoherence tomography (OCT) apparatus that obtains cross sectional imagesusing OCT, a retinal camera that photographs a fundus, a Scanning LaserOphthalmoscope (SLO) that obtains images of a fundus by laser scanningwith a confocal optical system, a slit lamp that obtains images byphotographing an optical section of a cornea using slit light, etc.

Moreover, examples of ophthalmologic measuring apparatuses include aneye refractivity examination apparatus (refractometer, keratometer) thatmeasures refractive properties of an eye, a tonometer, a specularmicroscope that obtains properties of a cornea (cornea thickness,cellular distribution, etc.), a wave-front analyzer that obtainsaberration information of an eye using a Shack-Hartmann sensor, etc.

Regarding ophthalmic examinations using these apparatuses, in terms ofprecision and accuracy of examinations, position adjustment between theoptical system of the apparatus and an eye is very important. Thisposition adjustment includes alignment and tracking. Alignment includesthe action of aligning the light axis of the optical system of theapparatus with respect to the axis of an eye (xy alignment), as well asthe action of adjusting the distance between the eye and the opticalsystem of the apparatus (z alignment). Tracking is an action ofdetecting the movement of an eye and changing the position of theoptical system of the apparatus in accordance with the eye.

PRIOR ART DOCUMENT

[Patent Document 1] Japanese Patent No. 4896794

[Patent Document 2] Japanese Unexamined Patent Application PublicationNo. 2013-5982

Problem to be Solved by the Invention

In the case in which examination is performed by entering light flaxinto an eye such as OCT, SLO and refractometer, it is impossible toproperly carry out the examination if there is a factor that disturbslight in the eye. For example, in the case of imaging the fundus of acataract eye by OCT, a problem occurs such as the deterioration of imagequality, impossibility of imaging the fundus, etc. if there is an opaqueportion of the crystalline lens on the path of the light flux. It shouldbe noted that there are disturbing causes other than cataract, forexample, opacity of a cornea, opacity of an aqueous humor, opacity of avitreous body, etc.

The objective of the present invention is to provide an ophthalmologicapparatus capable of carrying out examinations even when there is afactor that disturbs light in an eye.

Means for Solving the Problem

The invention of claim 1 is an ophthalmologic apparatus comprising: anexamination part configured to include an optical system for opticallyexamining an eye; a moving mechanism configured to move the opticalsystem; an information obtaining part configured to obtain informationfor carrying out position matching of the optical system to the eye; acontroller configured to carry out first control for the movingmechanism based on the information obtained by the information obtainingpart to move the optical system, determine whether information opticallyobtained by the optical system after the first control is appropriate tothe examination or not, and when it is determined that this informationis not appropriate, carry out second control for the moving mechanism inresponse to a prescribed trigger to move the optical system.

The invention of claim 2 is the ophthalmologic apparatus of claim 1,wherein the controller is configured to determine whether informationoptically obtained by the optical system after the second control isappropriate to the examination or not, and when it is determined thatthis information is not appropriate, carry out third control for themoving mechanism to move the optical system.

The invention of claim 3 is the ophthalmologic apparatus of claim 2,wherein the controller is configured to move the optical system in afirst direction by the second control, and move the optical system in asecond direction that is the opposite direction to the first directionby the third control.

The invention of claim 4 is the ophthalmologic apparatus of claim 3,wherein the controller is configured to move, by the second control, theoptical system to the position that is prescribed distance away in thefirst direction from the position after the movement by the firstcontrol, and move, by the third control, the optical system to theposition that is the prescribed distance away in the second directionfrom the position after the movement by the first control.

The invention of claim 5 is the ophthalmologic apparatus of claim 3,wherein the first direction is a downward direction or a sagittal linedirection.

The invention of claim 6 is the ophthalmologic apparatus of claim 1,wherein the optical system is configured to irradiate light from a lightsource onto an eye fundus, and detect returned light of this light fromthe eye fundus, and the controller is configured to perform thedetermination based on the detection result of the returned light.

The invention of claim 7 is the ophthalmologic apparatus of claim 6,wherein the optical system is configured to split light from the lightsource into signal light and reference light, scan the eye fundus withthe signal light, and detect interference light obtained by composingreturned light of the signal light from the eye fundus and the referencelight, the examination part is configured to include a cross sectionalimage forming part configured to form a cross sectional image of the eyefundus based on the detection result of the interference light by theoptical system, and the controller is configured to carry out thedetermination based on the detection result of the interference light orthe cross sectional image.

The invention of claim 8 is the ophthalmologic apparatus of claim 7,wherein the optical system is configured to include anoptical-path-length changing part configured for relatively changingoptical path length of the signal light and optical path length of thereference light the controller is configured to, in the determination,while controlling the optical system in such a way as to repeatedly scanthe same portion of the eye fundus, control the optical-path-lengthchanging part such that the eye fundus is depicted in a prescribed areain a frame based on detection results of the interference light or crosssectional images repeatedly obtained by this control, and determine thatthe information optically obtained by the optical system is notappropriate when the eye fundus is not depicted in the prescribed area.

The invention of claim 9 is the ophthalmologic apparatus of claim 1,wherein the controller is configured to display an object including afirst operating element on a display means when it is determined thatthe information optically obtained by the optical system after the firstcontrol is not appropriate, and the prescribed trigger is operation tothe first operating element performed using an operating means.

The invention of claim 10 is the ophthalmologic apparatus of claim 9,wherein the object includes a second operating element, and thecontroller is configured to carry out acquisition of information by theoptical system again when operation to the second operating element isperformed by using the operating means.

The invention of claim 11 is the ophthalmologic apparatus of claim 1,further comprising a front-image obtaining part configured to obtain afront image of the eye, wherein the controller is configured to display,on a display means, information indicating a previously determineddestination of the optical system over the front image when it isdetermined that the information optically obtained by the optical systemis not appropriate.

The invention of claim 12 is the ophthalmologic apparatus of claim 11,wherein the controller is configured to, when the display position ofthe information indicating the destination is changed by using anoperating means, carry out control of the moving mechanism such that theoptical system is moved to the destination after this change.

The invention of claim 13 is the ophthalmologic apparatus of claim 1,further comprising a front-image obtaining part configured to obtain afront image of the eye, wherein the controller is configured to displaythe front image on a display means, and when it is determined that theinformation optically obtained by the optical system after the firstcontrol is not appropriate and also when a position in the front imagedisplayed on the display means is designated by using an operatingmeans, carry out control of the moving mechanism such that the opticalsystem is moved to the designated position.

The invention of claim 14 is the ophthalmologic apparatus of claim 11 or13, further comprising a region-of-interest obtaining part configured toobtain information indicating a region of interest in the eye, whereinthe controller is configured to display the information indicating theregion of interest over the front image.

The invention of claim 15 is the ophthalmologic apparatus of claim 14,wherein the region-of-interest obtaining part is configured to obtainthe information indicating the region of interest based on an imageobtained by red reflex imaging previously performed to the eye.

The invention of claim 16 is the ophthalmologic apparatus of claim 1,wherein the information obtaining part is configured to include one ormore imaging part configured to obtain a moving image of an anterior eyepart of the eye, the controller is configured to carry out the firstcontrol based on the moving image.

The invention of claim 17 is the ophthalmologic apparatus of claim 16,wherein the information obtaining part is configured to include twoimaging parts non-coaxially arranged to the optical system, and a firstdisplacement calculator configured to calculate a displacement betweenthe eye and the optical system by analyzing two images substantiallysimultaneously obtained by the two imaging parts, and the controller isconfigured to carry out the first control based on the displacementcalculated by the first displacement calculator.

The invention of claim 18 is the ophthalmologic apparatus of claim 16,wherein the imaging part is coaxially arranged with the optical systemand obtains a moving image of the anterior eye part, and the informationobtaining part is configured to include an alignment optical systemconfigured to project an alignment target on the anterior eye part, anda second displacement calculator configured to calculate a displacementbetween the eye and the optical system by analyzing the moving image ofthe anterior eye part on which the alignment target is being projected,and the controller is configured to carry out the first control based onthe displacement calculated by the second displacement calculator.

The invention of claim 19 is the ophthalmologic apparatus of claim 1,wherein the controller is configured to, in the second control,interlockingly carry out control of causing the optical system torepeatedly perform acquisition of the optical information and control ofcausing the moving mechanism to stepwise move the optical system, anddetermine whether this interlocking control is continued or ended basedon information successively obtained by the optical system during thisinterlocking control.

Effect of the Invention

According to the present invention, it is possible to carry outexaminations even when there is a factor that disturbs light in an eye.

BRIEF EXPLANATION OF THE DRAWINGS

FIG. 1 is a schematic diagram showing an example of the configuration ofan ophthalmologic apparatus according to an embodiment.

FIG. 2 is a schematic diagram showing an example of the configuration ofan ophthalmologic apparatus according to an embodiment.

FIG. 3 is a schematic diagram showing an example of the configuration ofan ophthalmologic apparatus according to an embodiment.

FIG. 4A is a schematic diagram showing an example of the configurationof an ophthalmologic apparatus according to an embodiment.

FIG. 4B is a schematic diagram showing an example of the configurationof an ophthalmologic apparatus according to an embodiment.

FIG. 5A is a schematic diagram for explaining an operational example ofan ophthalmologic apparatus according to an embodiment.

FIG. 5B is a schematic diagram for explaining an operational example ofan ophthalmologic apparatus according to an embodiment.

FIG. 6 is a flowchart showing an operational example of anophthalmologic apparatus according to an embodiment.

FIG. 7A is a flowchart showing an operational example of anophthalmologic apparatus according to an embodiment.

FIG. 7B is a flowchart showing an operational example of anophthalmologic apparatus according to an embodiment.

FIG. 8A is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 8B is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 8C is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 8D is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 8E is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 8F is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 8G is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 8H is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 8I is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

FIG. 9A is a schematic diagram for explaining an operational example ofan ophthalmologic apparatus according to an embodiment.

FIG. 9B is a schematic diagram for explaining an operational example ofan ophthalmologic apparatus according to an embodiment.

FIG. 10 is a schematic diagram for explaining an operational example ofan ophthalmologic apparatus according to an embodiment.

FIG. 11 is a schematic diagram for explaining an operational example ofan ophthalmologic apparatus according to an embodiment.

FIG. 12 is a schematic diagram showing an example of a screen displayedby an ophthalmologic apparatus according to an embodiment.

MODE FOR CARRYING OUT THE INVENTION

Embodiments of ophthalmologic apparatuses related to the presentinvention are explained in detail with reference to diagrams.Ophthalmologic apparatuses related to the present invention are used foroptical examinations of an eye. Such ophthalmologic apparatuses includethe abovementioned ophthalmologic imaging apparatuses and ophthalmologicmeasuring apparatuses. The ophthalmologic imaging apparatuses include anOCT apparatus, a retinal camera, a scanning laser ophthalmoscope (SLO),a slit lamp, etc. Moreover, the ophthalmologic measuring apparatusesinclude an eye refractivity examination apparatus, a wave-frontanalyzer, a axial length measuring apparatus, etc. A case of applyingthe present invention to an optical coherence tomography apparatus isexplained in the following embodiments; however, the present inventionmay be applied to any other ophthalmologic apparatuses as well.

In this specification, an image obtained by optical coherence tomographyis sometimes referred to as an OCT image. Furthermore, a measuringaction for forming an OCT image is sometimes referred to as an OCTmeasurement. It should be noted that the contents of the documents citedin this specification may be employed in the following embodiments.

In the following embodiments, an OCT apparatus using OCT of so-calledspectral domain type is described; however, the present invention mayalso be applied to OCT apparatus using other types than spectral domain,such as swept source type and en-face type. It should be noted that theswept source OCT is a method of imaging the morphology of an object by:scanning (sweeping) the wavelength of light that is irradiated to theobject; acquiring the spectral intensity distribution by successivelydetecting interference light obtained from superposing the reflectedlights of the light of the respective wavelengths on reference light;and executing Fourier transform on the acquired spectral intensitydistribution. The en-face OCT is a method of irradiating light with apredetermined beam diameter to an object and analyzing the components ofinterference light obtained from superposing the reflected light thereofand reference light, thereby forming an image of a cross-section of theobject orthogonal to the travelling direction of the light, and it isalso referred to as full-field type.

An apparatus that is configured by combining an OCT apparatus and anretinal camera is explained in the following embodiment; however, thescope in which the present invention is applicable is not limited tosuch a combination apparatus. For example, the present invention may beapplied to an apparatus with other combination or an ophthalmologicapparatus with a single function (for example, a retinal camera alone).

First Embodiment [Configuration]

An ophthalmologic apparatus 1, as shown in FIG. 1, comprises a retinalcamera unit 2, an OCT unit 100, and an arithmetic and control unit 200.The retinal camera unit 2 has almost the same optical system as aconventional retinal camera. The OCT unit 100 is provided with anoptical system for obtaining an OCT image of a fundus. The arithmeticand control unit 200 is provided with a computer that executes variousarithmetic processes, control processes, and so on.

[Retinal Camera Unit]

The retinal camera unit 2 shown in FIG. 1 is provided with an opticalsystem for forming a two-dimensional image (fundus image) representingthe surface morphology of the fundus Ef of the eye E. Fundus imagesinclude observation images, captured images, etc. The observation imageis, for example, a monochrome moving image formed at a prescribed framerate using near-infrared light. It should be noted that when the opticalsystem is focused on the anterior eye part Ea of the eye, the retinalcamera unit 2 may obtain an observation image of the anterior eye partEa. The captured image is, for example, a color image captured byflashing visible light, or a monochrome still image using near-infraredlight or visible light as illumination light. The retinal camera unit 2may be configured to be capable of acquiring other types of images suchas a fluorescein angiography image, an indocyanine green fluorescentimage and a fundus autofluorescent image.

A jaw holder and forehead rest for supporting the face of the subject isprovided with the retinal camera unit 2. The jaw holder and foreheadrest correspond to the supporter 440 indicated in FIG. 4A and FIG. 4B.It should be noted that, in FIG. 4A and FIG. 4B, symbol 410 indicates abase in which a drive system such as an optical system driver 2A, etc.and arithmetic and control circuits are accommodated. Moreover, symbol420 indicates a case in which optical systems are accommodated, which isprovided on the base 410. Moreover, symbol 430 indicates a lens case inwhich an objective lens 22 is accommodated, which is provided as aprotrusion from the front surface of the case 420.

The retinal camera unit 2 is provided with an illumination opticalsystem 10 and an imaging optical system 30. The illumination opticalsystem 10 irradiates an illumination light to the fundus Ef. The imagingoptical system 30 guides a fundus reflected light of the illuminationlight to imaging devices (CCD image sensors (sometimes simply calledCCD) 35, 38). Moreover, the imaging optical system 30 guides signallight coming from the OCT unit 100 to the fundus Ef, and guides thesignal light propagated through the fundus Ef to the OCT unit 100.

An observation light source 11 of the illumination optical system 10comprises, for example, a halogen lamp. Light output from theobservation light source 11 (observation illumination light) isreflected by a reflection mirror 12 with a curved reflection surface,and becomes near-infrared after passing through a visible cut filter 14via a condenser lens 13. Furthermore, the observation illumination lightis once converged near an imaging light source 15, reflected by a mirror16, and passes through relay lenses 17, 18, diaphragm 19, and relay lens20. Then, the observation illumination light is reflected on theperipheral part (the surrounding region of an aperture part) of anaperture mirror 21, penetrates a dichroic mirror 46, and refracted by anobject lens 22, thereby illuminating the fundus Ef. It should be notedthat an LED (light emitting diode) may be used as the observation lightsource.

The fundus reflection light of the observation illumination light isrefracted by the object lens 22, penetrates the dichroic mirror 46,passes through the aperture part formed in the center region of theaperture mirror 21, passes through a dichroic mirror 55, travels througha focusing lens 31, and is reflected by a mirror 32. Furthermore, thefundus reflection light passes through a half-mirror 39A, is reflectedby a dichroic mirror 33, and forms an image on the light receivingsurface of the CCD image sensor 35 by a condenser lens 34. The CCD imagesensor 35 detects, for example, the fundus reflection light at a presetframe rate. An image (observation image) based on the fundus reflectionlight detected by the CCD image sensor 35 is displayed on a displaydevice 3. It should be noted that when the imaging optical system 30 isfocused on the anterior eye part, an observation image of the anterioreye part of the eye E is displayed.

The imaging light source 15 is configured, for example, by a xenon lamp.Light output from the imaging light source 15 (imaging illuminationlight) is irradiated to the fundus Ef via a route that is similar to theobservation illumination light. The fundus reflection light of theimaging illumination light is guided to the dichroic mirror 33 via thesame route as that of the observation illumination light, passes throughthe dichroic mirror 33, is reflected by a mirror 36, and forms an imageon the light receiving surface of the CCD image sensor 38 by a condenserlens 37. An image (captured image) based on the fundus reflection lightdetected by the CCD image sensor 38 is displayed on the display device3. It should be noted that the display device 3 for displaying anobservation image and the display device 3 for displaying a capturedimage may be the same or different. Furthermore, when similarphotographing is carried out by illuminating the eye E with infraredlight, an infrared captured image is displayed. Moreover, an LED may beused as the imaging light source.

An LCD (Liquid Crystal Display) 39 displays a fixation target or avisual target for measuring visual acuity. The fixation target is avisual target for fixating the eye E, and is used when photographing afundus or OCT measurement.

Part of the light output from the LCD 39 is reflected by a half-mirror39A, reflected by the mirror 32, travels through the focusing lens 31and the dichroic mirror 55, passes through the aperture part of theaperture mirror 21, penetrates the dichroic mirror 46, and is refractedby the object lens 22, thereby being projected to the fundus Ef.

By changing a display position of the fixation target on the screen ofthe LCD 39, a fixation position of the eye E is changed. Examples of thefixation position of the eye E includes a position for acquiring animage centered on the macula of the fundus Ef, a position for acquiringan image centered on the optic papilla, a position for acquiring animage centered on the fundus center between the macula and the opticpapilla, etc. as in conventional retinal cameras, for example. Moreover,it is possible to arbitrarily change the display position of thefixation target.

Furthermore, as with conventional retinal cameras, the retinal cameraunit 2 is provided with an alignment optical system 50 and a focusoptical system 60. The alignment optical system 50 generates a target(alignment target) for position matching of the optical system(examination optical system) with respect to the eye E (alignment). Thefocus optical system 60 generates a target (split target) for adjustingthe focus with respect to the eye E.

Light output from the LED 51 of the alignment optical system 50(alignment light) travels through diaphragms 52, 53 and a relay lens 54,is reflected by the dichroic mirror 55, passes through the aperture partof the aperture mirror 21, penetrates the dichroic mirror 46, and isprojected onto the cornea of the eye E by the object lens 22.

Cornea reflection light of the alignment light travels through theobject lens 22, the dichroic mirror 46 and the abovementioned aperturepart, and part of the cornea reflection light penetrates the dichroicmirror 55, passes through the focusing lens 31, is reflected by themirror 32, penetrates the half-mirror 39A, is reflected by the dichroicmirror 33, and is projected onto the light receiving surface of the CCDimage sensor 35 by the condenser lens 34. An image captured by the CCDimage sensor 35 (alignment target) is displayed on the display device 3along with the observation image. A user conducts alignment by anoperation that is the same as conventional retinal cameras. Instead,alignment may be performed in such a way that an arithmetic and controlunit 200 analyzes the position of the alignment target to move theoptical system (automatic alignment). It should be noted that, in thepresent embodiment, automatic alignment is possible using anterior eyecameras 300 (mentioned later); therefore, the ability of automaticalignment using the alignment target is not necessarily required.However, it is possible to configure it such that automatic alignmentmay be carried out using the alignment target when automatic alignmentusing the anterior eye cameras 300 fails or the like, or to configure itsuch that automatic alignment using the anterior eye cameras 300 andautomatic alignment using the alignment target may be selectively used.

In order to conduct focus adjustment, the reflection surface of areflection rod 67 is arranged in a slanted position in the light path ofthe illumination optical system 10. Light output from an LED 61 of thefocus optical system 60 (focus light) passes through a relay lens 62, issplit into two light fluxes by a split target plate 63, passes through atwo-hole diaphragm 64, is reflected by a mirror 65, and is reflectedafter an image is formed once on the reflection surface of thereflection rod 67 by a condenser lens 66. Furthermore, the focus lighttravels through the relay lens 20, is reflected by the aperture mirror21, penetrates the dichroic mirror 46, and is refracted by the objectlens 22, thereby being projected on the fundus Ef.

The fundus reflection light of the focus light passes through the sameroute as the cornea reflection light of the alignment light and isdetected by the CCD image sensor 35. An image captured by the CCD imagesensor 35 (split target) is displayed on the display device 3 along withan observation image. The arithmetic and control unit 200, as in theconventional case, analyzes the position of the split target, and movesthe focusing lens 31 and the focus optical system 60 for focusing(automatic focusing). It should be noted that focusing may be performedmanually while visually recognizing the split target.

The dichroic mirror 46 branches the optical path for OCT measurementfrom the optical path for fundus photography. The dichroic mirror 46reflects light of the wavelength band used in OCT measurement andtransmits light for fundus photography. This optical path for OCTmeasurement is provided with, in order from the OCT unit 100 side, acollimator lens unit 40, an optical-path-length changing part 41, agalvano scanner 42, a focusing lens 43, a mirror 44, and a relay lens45.

The optical-path-length changing part 41 is movable in the direction ofthe arrow indicated in FIG. 1, thereby changing the length of theoptical path for OCT measurement. This change in the optical path lengthis used for correcting the optical path in accordance with the axiallength of the eye E, adjusting the interference state, etc. Theoptical-path-length changing part 41 is configured to include, forexample, a corner cube and a mechanism for moving this.

The galvano scanner 42 changes the travelling direction of light (signallight LS) travelling along the optical path for OCT measurement.Thereby, the fundus Ef may be scanned using the signal light LS. Thegalvano scanner 42 is configured to include, for example, a galvanomirror for scanning with the signal light LS in the x direction, agalvanometer mirror for scanning in the y direction, and a mechanism forindependently driving these. Accordingly, the signal light LS may bescanned in any direction on the xy plane.

The retinal camera unit 2 is provided with anterior eye cameras 300. Theanterior eye cameras 300 substantially and simultaneously photograph ananterior eye part Ea from different directions. In the presentembodiment, two cameras are provided on the surface of the retinalcamera unit 2 of the subject side (refer to the anterior eye cameras300A and 300B indicated in FIG. 4A). Moreover, the anterior eye cameras300A and 300B are, as indicated in FIG. 1 and FIG. 4A, provided inpositions away from the optical path of an illumination optical system10 and the optical path of an imaging optical system 30. In other words,the anterior eye cameras 300A and 300B are non-coaxially arranged to theillumination optical system 10 and the imaging optical system 30.Hereinafter, the two anterior eye cameras 300A and 300B may becollectively represented by the symbol 300.

In the present embodiment, two anterior eye cameras 300A and 300B areprovided; however, the number of anterior eye cameras in an embodimentmay be any number of two or more (It should be noted that an anterioreye camera is not necessarily provided in the case of using an alignmenttarget). However, when taking into consideration the arithmetic process(mentioned later), it is sufficient that a configuration is capable ofsubstantially and simultaneously photographing the anterior eye partfrom two different direction. Moreover, in the present embodiment, theanterior eye camera 300 is separately provided from the illuminationoptical system 10 and imaging optical system 30; however, the similaranterior-eye photography may be performed using at least the imagingoptical system 30. That is, one from among two or more anterior eyecameras may be a configuration comprising the imaging optical system 30.In any case, it is sufficient in the present embodiment that theanterior eye part may be substantially and simultaneously photographedfrom two (or more) different directions.

It should be noted that “substantially simultaneous” indicates allowinga time lag of the photographing timings by a degree of being able toignore eye movements when photographing using two or more anterior eyecameras. Accordingly, images in which the eye E is in substantially thesame position (direction) may be acquired by the two or more anterioreye cameras.

Moreover, photographing using the two or more anterior eye cameras maybe a moving image photographing or a still image photographing; however,in the present embodiment, a case of carrying out moving imagephotographing is explained in greater detail. In the case of movingimage photographing, substantial and simultaneous photographing of theanterior eye part mentioned above may be realized by means ofcontrolling to match the timings for commencing photographing, orcontrolling frame rates and/or the timings for capturing respectiveframes. Meanwhile, in the case of still image photographing, this may berealized by controlling so as to match the timings for photographing.

[OCT Unit]

The configuration of the OCT unit 100 will be described with referenceto FIG. 2. The OCT unit 100 is provided with an optical system forobtaining an OCT image of the fundus Ef. The optical system has asimilar configuration to a conventional Fourier-domain-type OCTapparatus. That is to say, the optical system is configured to splitlight (e.g. low-coherence light) from a light source into referencelight and signal light, make the signal light propagated through afundus and the reference light propagated through a reference opticalpath interfere with each other to generate interference light, anddetect the spectral component of this interference light. This detectionresult (detection signal) is transmitted to the arithmetic and controlunit 200.

It should be noted that, in the case of swept source type OCT apparatus,a wavelength sweeping light source (swept source) is provided instead ofa light source outputting low-coherence light, while an optical elementfor spectrally decomposing interference light is not provided.Generally, regarding the configuration of the OCT unit 100, knowntechnologies may be applied according to the type of OCT.

The light source unit 101 outputs a broadband, low-coherence light L0.The low-coherence light L0 includes, for example, a near-infraredwavelength band (approximately 800 nm to 900 nm), and has a temporalcoherence length of around several tens of micrometers. It should benoted that, a wavelength band that is not visible to human eyes, such asnear-infrared light with a central wavelength of around 1040 to 1060 nm,for example, may be used as the low-coherence light L0.

The light source unit 101 is configured to include light output device,such as an SLD (super luminescent diode), LED, SOA (SemiconductorOptical Amplifier) and the like.

The low coherence light L0 output from the light source unit 101 isguided to a fiber coupler 103 by an optical fiber 102 and split intosignal light LS and reference light LR.

The reference light LR is guided by the light fiber 104 and arrives atan optical attenuator (attenuator) 105. The optical attenuator 105automatically adjusts the light amount of the reference light LR guidedby the light fiber 104 under the control of the arithmetic and controlunit 200 using known technologies. The reference light LR with the lightamount having adjusted by the optical attenuator 105 is guided by thelight fiber 104, arriving at a polarization adjuster (polarizationcontroller) 106. The polarization adjuster 106 is an apparatus that, bymeans of applying external stress to a looped light fiber 104, adjuststhe polarization condition of the reference light LR guided in the lightfiber 104. It should be noted that the configuration of the polarizationadjuster 106 is not limited to this and any known technologies may beused. The reference light LR with adjusted polarization condition by thepolarization adjuster 106 arrives at the fiber coupler 109.

The signal light LS generated by the fiber coupler 103 is guided by thelight fiber 107 and becomes a parallel light flux by means of thecollimator lens unit 40. Further, the signal light LS arrives at thedichroic mirror 46 via the optical-path-length changing part 41, thegalvano scanner 42, the focusing lens 43, the mirror 44, and the relaylens 45. Subsequently, the signal light LS is reflected by the dichroicmirror 46, refracted by the objective lens 22, and projected onto thefundus Ef. The signal light LS is scattered (including reflections) atvarious depth positions of the fundus Ef. A back-scattered light of thesignal light LS from the fundus Ef reversely advances along the samepath as the outward path and is guided to the fiber coupler 103,arriving at the fiber coupler 109 via the light fiber 108.

The fiber coupler 109 causes the back-scattered light of the signallight LS and the reference light LR having passed through the opticalfiber 104 to interfere with each other. Interference light LC thusgenerated is guided by an optical fiber 110 and output from an exit end111. Furthermore, the interference light LC is converted to a parallellight flux by a collimator lens 112, spectrally divided (spectrallydecomposed) by a diffraction grating 113, converged by the convergencelens 114, and projected onto the light receiving surface of a CCD imagesensor 115. It should be noted that although the diffraction grating 113shown in FIG. 2 is of the transmission type, it is possible to use aspectrally decomposing element of any other type, such as a diffractiongrating of reflection type.

The CCD image sensor 115 is for example a line sensor, and detects therespective spectral components of the spectrally decomposed interferencelight LC and converts the components into electric charges. The CCDimage sensor 115 accumulates these electric charges to generate adetection signal, and transmits the signal to the arithmetic and controlunit 200.

Although a Michelson-type interferometer is employed in this embodiment,it is possible to employ any type of interferometer such as aMach-Zehnder-type as necessary. Instead of a CCD image sensor, othertypes of image sensors, such as a CMOS (Complementary Metal OxideSemiconductor) image sensor, can be used.

[Arithmetic and Control Unit]

A configuration of the arithmetic and control unit 200 will bedescribed. The arithmetic and control unit 200 analyzes the detectionsignals input from the CCD image sensor 115 to form an OCT image of thefundus Ef. An arithmetic process for this is the same as that of aconventional Fourier-domain-type OCT apparatus.

Further, the arithmetic and control unit 200 controls each part of theretinal camera unit 2, the display device 3 and the OCT unit 100. Forexample, the arithmetic and control unit 200 causes the display device 3to display an OCT image G of the fundus Ef.

Moreover, as control of the retinal camera unit 2, the arithmetic andcontrol unit 200 executes: control of actions of the observation lightsource 11, the imaging light source 15 and the LED's 51 and 61; controlof action of the LCD 39; control of movements of the focusing lenses 31and 43; control of movement of the reflection rod 67; control ofmovement of the focus optical system 60; control of movement of theoptical path length changing part 41; control of action of the galvanoscanner 42; control of actions of the anterior eye cameras 300; and soon.

Further, as control of the OCT unit 100, the arithmetic and control unit200 executes: control of action of the light source unit 101; control ofaction of the optical attenuator 105; control of action of thepolarization adjuster 106; control of action of the CCD image sensor115; and so on.

The arithmetic and control unit 200 includes a microprocessor, a RAM, aROM, a hard disk drive, a communication interface, and so on, as inconventional computers. The storage device such as a hard disk drivestores computer programs for controlling the ophthalmologic apparatus 1.The arithmetic and control unit 200 may be provided with various kindsof circuit boards, such as a circuit board for forming OCT images.Moreover, the arithmetic and control unit 200 may be provided withoperation devices (input devices) such as a keyboard and a mouse, and/ordisplay devices such as an LCD.

The retinal camera unit 2, the display device 3, the OCT unit 100, andthe arithmetic and control unit 200 may be integrally configured (thatis, within a single case), or configured as two of more separated cases.

[Control System]

A configuration of a control system of the ophthalmologic apparatus 1will be described with reference to FIG. 3.

(Controller)

The control system of the ophthalmologic apparatus 1 has a configurationwith a controller 210 as a center. The controller 210 includes, forexample, the aforementioned microprocessor, RAM, ROM, hard disk drive,and communication interface. The controller 210 is provided with a maincontroller 211, a storage 212, an optical system position obtaining part213 and an information determining part 214.

(Main Controller)

The main controller 211 carries out various kinds of controls mentionedabove. It should be noted that the movement control of the focusing lens31 is configured to control a focus driver (not illustrated) to move thefocusing lens 31 in the optical axis direction. Thereby, the focusposition of the imaging optical system 30 is changed. Moreover, controlof the motion of the focusing lens 43 is to move the focusing lens 43 inthe optical axis direction by controlling a focus driver (notillustrated). Thereby, focus position of the signal light LS is changed.

The main controller 211 is capable of controlling the optical systemdriver 2A to three-dimensionally move the optical system installed inthe retinal camera unit 2. This control is carried out upon automaticalignment and/or tracking. Here, tracking refers to moving the opticalsystem of the apparatus in accordance with the eye movement of the eyeE. Tracking is carried out at, for example, the stage after alignment(depending on the conditions, focusing is also carried out in advance).Tracking is a function causing the position of the optical system of theapparatus to follow the eye movement, thereby maintaining a suitablepositional relationship in which alignment (and focusing) is matched.

It should be noted that the optical system driver 2A of the presentembodiment moves the optical system installed in the retinal camera unit2; however, a configuration is possible in which the optical systeminstalled in the retinal camera unit 2 and the optical system installedin the OCT unit 100 are moved by means of the optical system driver 2A.The optical system driver 2A is an example of a “moving mechanism.”

Moreover, the anterior eye cameras 300 of the present embodiment areprovided on the case of the retinal camera unit 2; accordingly, theanterior eye cameras 300 can be moved by means of controlling theoptical system driver 2A (camera moving part). Moreover, it is possibleto provide a camera moving part capable of independently moving the twoor more anterior eye cameras 300, respectively. Specifically, the cameramoving part may be configured to include driving mechanisms (actuator,power transmission mechanism, etc.) provided with respect to eachanterior eye camera 300. Moreover, the camera moving part may beconfigured to move two or more anterior eye cameras 300 by transmittingthe power generated by a single actuator by means of the powertransmission mechanism provided for each anterior eye camera 300.

The main controller 211 executes a process of writing data into thestorage 212, and a process of reading out data from the storage 212.

The storage 212 stores various kinds of data. The data stored in thestorage 212 is, for example, image data of OCT images, image data offundus images, and eye information. The eye information includesinformation on a subject such as a patient ID and a name, information onan eye such as identification information of left eye or right eye, andso on. Moreover, various kinds of programs and data in order to operatethe ophthalmologic apparatus 1 are stored in the storage 212.

Aberration information 212 a is stored in the storage 212 in advance.The aberration information 212 a includes information, for each anterioreye camera 300, regarding the distortion aberration occurred in aphotograph image due to effects by the optical system installed therein.Here, the optical system installed in the anterior eye camera 300includes, for example, optical elements occurring distortion aberrationof lenses, etc. It may be said that the aberration information 212 a isa parameter that quantifies the deformation of the photograph imagescaused by these optical elements.

An example of a method for generating the aberration information 212 ais explained. Taking into consideration instrumental error (differencein distortion aberration) of the anterior eye cameras 300, the followingmeasurements are carried out for each anterior eye camera 300. Anoperator prepares specific reference points. The reference points arephotographing target used in detecting the distortion aberration. Theoperator performs photographing multiple times while changing therelative position between the reference points and the anterior eyecameras 300. Accordingly, multiple photograph images of the referencepoints photographed from different directions may be obtained. Theoperator analyzes the multiple acquired photograph images, therebygenerating the aberration information 212 a of this anterior eye camera300. It should be noted that the computer that performs this analysisprocess may be an image processor 230 or any other computer (computerfor inspection before shipping products, computer for maintenance,etc.).

The analysis processes for generating the aberration information 212 ainclude, for example, the following procedures:

an extraction procedure for extracting image regions corresponding tothe reference points in each photograph image;

a distribution state calculating procedure for calculating thedistribution state (coordinates) of the image regions corresponding tothe reference points in each photograph image;

a distortion aberration calculating procedure for calculating aparameter indicating the distortion aberration based on the obtaineddistribution state; and

a correction factor calculating procedure for calculating a factor forcorrecting the distortion aberration based on the obtained parameter.

It should be noted that the parameter related to the distortionaberration that is given to an image by the optical system may includethe principal distance, the position of a principal point (verticallyand horizontally), the distortion of a lens (radiation direction andtangential direction), etc. The aberration information 212 a isconstructed as information (for example, table information) thatassociates the identification information of each anterior eye camera300 and the correction factor corresponding thereto. The aberrationinformation 212 a generated in this manner is stored in the storage 212by the main controller 211. Generation of such aberration information212 a and the aberration correction process based on this is referred toas camera calibration, etc.

(Optical System Position Obtaining Part)

The optical system position obtaining part 213 obtains the currentposition of the examination optical system installed in theophthalmologic apparatus 1. The examination optical system is theoptical system used for optically examining the eye E. The examinationoptical system in the ophthalmologic apparatus 1 of the presentembodiment (combined machine of the retinal camera and OCT apparatus) isthe optical system for obtaining images of an eye.

The optical system position obtaining part 213 receives informationpresenting the content of the movement control of the optical systemdriver 2A by means of the main controller 211, and obtains the currentposition of the examination optical system moved by the optical systemdriver 2A. A detailed example of this process will be explained. Themain controller 211 controls the optical system driver 2A at apredetermined timing (upon start-up of the apparatus, upon inputtingpatient information, etc.) and moves the examination optical system to apredetermined initial position. Thereafter, the main controller 211stores the control content each time the optical system driver 2A iscontrolled. Thereby, a history of the control contents may be obtained.The optical system position obtaining part 213 refers to this historyand obtains the control contents to date, and determines the currentposition of the examination optical system based on these controlcontents.

Moreover, each time the main controller 211 controls the optical systemdriver 2A, the control contents thereof may be transmitted to theoptical system position obtaining part 213, and the current position ofthe examination optical system may be obtained each time the opticalsystem position obtaining part 213 receives the control contents.

As another configuration example, the position sensor detecting theposition of the examination optical system may be provided with theoptical system position obtaining part 213.

When the current position of the examination optical system is obtainedby the optical system position obtaining part 213 as stated above, themain controller 211 is capable of, based on the obtained currentposition and the three-dimensional position of the eye E obtained by ananalyzer 231 (mentioned later), causing the optical system driver 2A tomove the examination optical system. Specifically, the main controller211 recognizes the current position of the examination optical systemfrom the acquisition result by the optical system position obtainingpart 213, and recognizes the three-dimensional position of the eye Efrom the analysis result by the analyzer 231. Subsequently, in orderthat the position of the examination optical system with respect to thethree-dimensional position of the eye E becomes a predeterminedpositional relationship, the main controller 211 changes the positionthereof with the current position of the examination optical system asthe starting point. This predetermined positional relationship may besuch that the positions in the x and y directions respectively coincide,while the distance in the z direction becomes a predetermined workingdistance.

(Information Determining Part)

The information determining part 214 determines whether or notinformation obtained from OCT is appropriate for carrying out OCT. theinformation obtained from OCT may be a detection signal from the CCDimage sensor 115 of the OCT unit 100, or information obtained byexecuting a prescribed process on this detection signal. Examples of thelatter include the following information: a cross sectional image (e.g.A-scan image, two-dimensional cross sectional image) formed by an imageforming part 220 based on the detection signals; information obtained inthe halfway stage of this cross sectional image formation; information(e.g. image etc.) formed by the image processor 230 based on one or morecross sectional images; information obtained by executing a processother than these on the detection signal.

An example of a determination process based on a detection signal fromthe CCD image sensor 115 is explained. The information determining part214 analyzes the detection signal to derive information indicating acharacteristic thereof (characteristic information), and determineswhether or not this characteristic information is appropriate forcarrying out OCT. Types of the characteristic information may bedetermined in advance based on an influence on the signal light LS (thatis, an influence on the interference light LC) from an intraocularfactor that disturbs light.

Intensity (amplitude etc.) is an example of the characteristicinformation. For example, when the signal light LS passes through anopaque portion in the eye E, the intensity of the signal light LSdecreases, thereby the intensity of the interference light LC decreases.The information determining part 214 derives the intensity of thedetection signal obtained by detecting the interference light LC, andcompares this intensity with a threshold. When the intensity is equal toor less than the threshold, the information determining part 214determines that this detection signal is not appropriate. This thresholdis defined in advance, for example, based on the intensity of lightoutput from the light source unit 101. It should be noted that thethreshold may be defined by taking account of various factors such asthe light splitting ratio of the fiber coupler 103, light attenuationamounts by optical elements, or the standard attenuation amount of lightthat passes through a healthy eye. Moreover, an amount of noises and SNratio are examples of the characteristic information other than signalintensity.

Even when taking account of information obtained in the halfway stage ofthe cross sectional image formation or information obtained by executinga process other than image formation on the detection signal, it iscapable of applying a similar process to the case of taking account ofthe detection signal. Moreover, the same applies to the case of takingaccount of information generated by the image processor 230 (forexample, information other than images) based on one or more crosssectional images formed by the image forming part 220.

Examples of determination processes in the case of taking account of across sectional image (A-scan image, two-dimensional cross sectionalimage, etc.) formed by the image forming part 220 or a cross sectionalimage (three-dimensional image etc.) formed by the image processor 230.A two-dimensional or three-dimensional cross sectional image is obtainedby changing the irradiation position of the signal light LS on thefundus Ef (that is, by scanning the fundus Ef with the signal light LS).If there is an opaque portion on at least a part of the trajectory ofthe scanning, there are cases in which the image quality of the A-scanimage (one-dimensional image along the depth direction) based on thesignal light LS having passed the opaque portion is deteriorated, oreven the fundus Ef is not imaged.

The information determining part 214 analyzes respective A-scan imagesincluded in a cross sectional image to calculate an evaluation value ofimage quality, and compares this evaluation value with a threshold. Whenthe evaluation value is equal to or less than the threshold, theinformation determining part 214 determines that this A-scan image isnot appropriate. The information determining part 214 carries out thisprocess for all A-scan images, thereby obtaining the distribution ofA-scan images (that is, scanning positions) determined to be appropriateand A-scan images (that is, scanning positions) determined to be notappropriate.

It should be noted that this threshold may be defined in advance, or setin the determination process. As an example of the latter, the thresholdmay be defined by statistically processing distribution (e.g. histogram)of multiple evaluation values calculated in the determination process.

Moreover, the evaluation value may be an arbitrary index indicatingimage quality of an A-scan image. For example, it is possible to obtainthe evaluation value based on distribution of brightness in an A-scanimage. As a specific example thereof, it is possible to derive, as anevaluation value, the contrast of an A-scan image, such as thedifference or ratio between high brightness parts (pixels correspondingto tissues with high reflectance) and low brightness parts (pixelscorresponding to tissues with low reflectance).

Another example of a process carried out by the information determiningpart 214 is explained. This determination process determines whether theprocess called Auto-Z has succeeded or failed. The Auto-Z is a functionfor depicting the image of the fundus Ef within a prescribed area(target area) in the frame of an OCT image (cross sectional image).

In the Auto-Z, the same positions of the fundus Ef are repeatedlyscanned. The trajectory of the respective scans is, for example, oflinear shape (line scanning). The information determining part 214analyzes each of the cross sectional images that are successivelyacquired by the repetitive scanning, thereby specifying, in real time,the depthwise position (position in the z-direction (depthwisedirection)) in the frame at which the image of a prescribed tissue (e.g.the surface of the fundus, a layer tissue with high brightness) of thefundus Ef is depicted. Furthermore, the information determining part 214calculates the displacement between the specified depthwise position andthe target area. The main controller 211 adjusts the difference of theoptical path length between the signal light LS and the reference lightLR such that the calculated displacement is cancelled, that is, suchthat the image of the prescribed tissue is depicted in the target area.

The adjustment of the difference of the optical path length is carriedout by controlling the optical-path-length changing part 41 to changethe optical path length of the signal light LS. It should be noted thatit is possible to apply a configuration to change the optical pathlength of the reference light LR (for example, a variable referencemirror (described later)). Moreover, it is possible to apply both the aconfiguration for changing the optical path length of signal light and aconfiguration for changing the optical path length of reference light.

The main controller 211 and the information determining part 214 carryout the above-mentioned process for the respective cross sectionalimages (or thinning-out of the cross sectional images is applied)obtained by the repetitive scanning. When the above-mentioneddisplacement becomes equal to or less than the threshold by a prescribedtiming, that is, when the image of the prescribed tissue is depictedwithin the target area by the prescribed timing, the informationdetermining part 214 determines that the Auto-Z succeeds.

In contrast, when the above-mentioned displacement does not become equalto or less than the threshold by the prescribed timing, that is, whenthe image of the prescribed tissue is not depicted within the targetarea by the prescribed timing, the information determining part 214determines that the Auto-Z is failed. It should be noted that thisprescribed timing is set in advance, and may be defined as the number oftimes of comparison between the above-mentioned displacement and thethreshold, or as the elapsed time from the beginning of the Auto-Z.

In the present example, the success (or failure) of the Auto-Zcorresponds to the fact that information obtained by the optical systemis appropriate (or not appropriate) for performing OCT. It should benoted that scattering or absorption of the signal light LS due to anopaque portion of the eye E is considered as a factor of failure of theAuto-Z.

The information determining part 214 may be configured to carry out adetermination process based on any evaluation value relating the imagequality of a cross sectional image instead of the success/failure of theAuto-Z.

(Image Forming Part)

The image forming part 220 forms image data of a cross sectional imageof the fundus Ef based on the detection signals from the CCD imagesensor 115. Like the conventional spectral-domain-type OCT, this processincludes processes such as noise elimination (noise reduction),filtering and FFT (Fast Fourier Transform). In the case of other typesof OCT apparatus, the image forming part 220 executes known processes inaccordance with the type thereof.

The image forming part 220 is configured to include, for example, theaforementioned circuit boards. It should be noted that “image data” andthe “image” based on this may be identified with each other in thisspecification.

(Image Processor)

The image processor 230 executes various image processes and analysis onimages formed by the image forming part 220. For example, the imageprocessor 230 executes various correction processes such as luminancecorrection and dispersion compensation of images. Moreover, the imageprocessor 230 executes various image processes and analysis on images(fundus images, anterior eye images, etc.) obtained by the retinalcamera unit 2.

The image processor 230 executes known image processes such as aninterpolation process of interpolating pixels between cross sectionalimages, thereby forming a three-dimensional image data of the fundus Ef.The three-dimensional image data refers to image data that the positionsof pixels are defined by the three-dimensional coordinates. Thethree-dimensional image data is, for example, image data composed ofthree-dimensionally arranged voxels. This image data is referred to asvolume data, voxel data, or the like. For displaying an image based onthe volume data, the image processor 230 executes a rendering process(such as volume rendering and MIP (Maximum Intensity Projection)) onthis volume data to form image data of a pseudo three-dimensional imagetaken from a specific view direction. This pseudo three-dimensionalimage is displayed on the display 241.

Further, it is also possible to form stack data of multiple crosssectional images as a three-dimensional image data. Stack data is imagedata obtained by three-dimensionally arranging multiple cross sectionalimages obtained along multiple scanning lines, based on the positionalrelation of the scanning lines. That is to say, stack data is image dataobtained by expressing multiple cross sectional images defined byoriginally individual two-dimensional coordinate systems by athree-dimensional coordinate system (namely, embedding into athree-dimensional space).

Further, the image processor 230 may form a cross sectional image at anarbitrary cross section based on a three-dimensional image data. Thisprocess is called MPR (Multi-Planar Reconstruction) and the like, andincludes a process of extracting picture elements (voxels) located at adesignated cross section and a process of arranging the extractedpicture elements.

Further, the image processor 230 is provided with an analyzer 231, animage determination part 232, and an image synthesis part 233.

(Analyzer)

The analyzer 231 analyzes two or more photograph images substantiallyand simultaneously obtained by two or more anterior eye cameras 300,thereby obtaining the three-dimensional position of the eye E. As anexample of a configuration for performing this process, the analyzer 231is provided with an image correction part 2311, characteristic positionspecifying part 2312, and a three-dimensional position calculating part2313.

(Image Correction Part)

The image correction part 2311 corrects the distortion of eachphotograph image obtained by the anterior eye cameras 300 based on theaberration information 212 a stored in the storage 212. This process maybe carried out by, for example, known image process technology based ona correction factor for correcting distortion aberration. It should benoted that, for cases in which the distortion aberration caused inphotograph images due to the optical system of the anterior eye cameras300 is sufficiently small, etc., there is no need to provide theaberration information 212 a and the image correction part 2311.

(Characteristic Position Specifying Part)

The characteristic position specifying part 2312 analyzes eachphotograph image (with the distortion aberration corrected by the imagecorrection part 2311), thereby specifying the position in the photographimage corresponding to the predetermined characteristic part of theanterior eye part Ea (referred to as the characteristic position). Asthe predetermined characteristic part, for example, the center of thepupil or the corneal apex of the eye E may be used. Hereinafter, aspecific example of a process for specifying the center of the pupil isexplained.

First, the characteristic position specifying part 2312 specifies theimage region (pupillary region) corresponding to the pupil of the eye Ebased on the distribution of the pixel values (luminous values, etc.) ina photograph image. Generally, the pupil is represented with lowerluminance compared to other parts, so the pupillary region may bespecified by searching an image region with low luminance. At this time,the pupillary region may be specified taking into consideration theshape of the pupil. That is, a configuration is possible of specifyingthe pupillary region by means of searching a substantially circularimage region with low luminance.

Next, the characteristic position specifying part 2312 specifies thecenter position of the specified pupillary region. As mentioned above,the pupil is substantially circular; therefore, it is possible tospecify the contour of the pupillary region, specify the center positionof this contour (an approximate circle or an approximate ellipsethereof), and treat this as the center of the pupil. Instead, it ispossible to derive the center of gravity of the pupillary region andtreat this center of gravity as the center of the pupil.

It should be noted that even when specifying the characteristic positioncorresponding to other characteristic part, it is possible to specifythe characteristic position based on the pixel value distribution of thephotograph image in the same manner as those mentioned above.

(Three-Dimensional Position Calculating Part)

The three-dimensional position calculating part 2313 calculates thethree-dimensional position of the eye E based on the positions of two ormore anterior eye cameras 300 and the characteristic positions in thetwo or more photograph images specified by the characteristic positionspecifying part 2312. This process is explained with reference to FIG.5A and FIG. 5B.

FIG. 5A is a top view illustrating the positional relationship betweenthe eye E and the anterior eye cameras 300A and 300B. FIG. 5B is a sideview illustrating the positional relationship between the eye E and theanterior eye cameras 300A and 300B. The distance (base line length)between the two anterior eye cameras 300A and 300B is represented as“B.” The distance (photographing distance) between the base line of thetwo anterior eye cameras 300A and 300B and a characteristic part P ofthe eye E is represented as “H.” The distance (screen distance) betweenthe respective anterior eye cameras 300A and 300B and a screen planethereof is represented as “f.”

In such an arrangement state, the resolution of images photographed bythe anterior eye cameras 300A and 300B is expressed by the followingformula. Here, Δp represents the pixel resolution.

xy resolution (planar resolution): Δxy=H×Δp/f

z resolution (depth resolution): Δz=H×H×Δp/(B×f)

The three-dimensional position calculating part 2313 applies knowntrigonometry, taking into consideration the positional relationshipindicated in FIG. 5A and FIG. 5B, to the positions of the two anterioreye cameras 300A and 300B (these are known) and the characteristicpositions corresponding to the characteristic part P in the twophotograph images, thereby calculating the three-dimensional position ofthe characteristic part P, that is, the three-dimensional position ofthe eye E.

The three-dimensional position of the eye E calculated by thethree-dimensional position calculating part 2313 is transmitted to thecontroller 210. Based on this calculation result of thethree-dimensional position, the controller 210 controls the opticalsystem driver 2A such that the optical axis of the examination opticalsystem matches the axis of the eye E and such that the distance of theexamination optical system with respect to the eye E becomes thepredetermined working distance. Here, the working distance is a presetvalue also referred to as the working distance, meaning the distancebetween the eye E and the examination optical system when performingexamination using the examination optical system.

Moreover, when the anterior eye cameras 300 parallelly photograph movingimages of the anterior eye part Ea from different directions, trackingof the examination optical system with respect to the movement of theeye E becomes possible by carrying out, for example, the followingprocesses (1) and (2).

(1) The analyzer 231 successively analyzes the two or more framessubstantially and simultaneously obtained by photographing movingpictures using two or more anterior eye cameras 300, therebysuccessively obtaining the three-dimensional positions of the eye E.

(2) The controller 210 successively controls the optical system driver2A based on the three-dimensional positions of the eye E successivelyobtained by the analyzer 231, thereby causing the position of theexamination optical system to follow the movement of the eye E.

The analyzer 231 may derive the displacement between the eye E and theexamination optical system based on the three-dimensional positionobtained by the three-dimensional position calculating part 2313. Thisprocess may be carried out by utilizing the fact that the positions ofthe anterior eye cameras 300 and the position of the examination opticalsystem are known. Here, the position of the examination optical systemis a position given in advance, and is, for example, the intersectingposition of the front surface (surface facing the eye E) of theobjective lens 22 and the optical axis of the examination opticalsystem. The analyzer 231 that carries out this process corresponds to a“first displacement calculator.”

Another example of a process for deriving the displacement between theeye E and the examination optical system is explained. In the presentexample, the alignment target is projected on the anterior eye part ofthe eye E. Further, a moving picture of the anterior part on which thealignment target is being projected is acquired by the retinal cameraunit 2. In general, a pair of alignment targets is displayed in each ofthe frames of this moving picture. The analyzer 231 calculates theobjective displacement based on the displayed position of the pair ofthe alignment targets.

This process is explained more specifically. When the examinationoptical system is positioned in a prescribed examination positionrelative to the eye E, the pair of the alignment targets is displayedover a prescribed position of the frame (for example, the center of theframe). The examination position corresponds to the positionalrelationship between the eye E and the examination optical system suchthat, for example, the x-coordinate and the y-coordinate of theprescribed site of the eye E (e.g. the corneal apex, the center of thepupil) and the x-coordinate and the y-coordinate of the examinationoptical system are substantially equal, and such that the distancebetween the eye E and the examination optical system (e.g. the objectivelens 22) is substantially equal to the prescribed working distance.Further, the gap (first gap) between the displayed positions of the twoalignment targets reflects the displacement from the working distance inthe z-direction, and the gap (second gap) of the displayed positions ofthe alignment targets relative to the prescribed position of the framereflects the displacement from the prescribed site of the eye E in thexy-direction. The analyzer 231 utilizes this relationship to derive thedisplacement in the z-direction from the first gap and the displacementin the xy-direction from the second gap. Thereby, the three-dimensionaldisplacement between the eye E and the examination optical system isobtained. It should be noted that such a process for calculating adisplacement is a process carried out in a known automatic alignment.The analyzer 231 that carries out this process corresponds to a “seconddisplacement calculator.”

(Image Determination Part)

The image determination part 232 analyzes a photograph image(s) obtainedby at least one from among two or more anterior eye cameras 300, therebydetermining whether or not the image of the anterior eye part Ea iswithin the predetermined area in this photograph image(s).

This predetermined area is set in advance within the photographingregion of the anterior eye camera 300, for example, set as a regionincluding the center of this photographing region. Here, the range ofthis predetermined area may be changed in accordance with thephotographing conditions of the anterior eye camera 300 (the position,the photographic magnification, etc. of the anterior eye camera 300).Moreover, the range of this predetermined area may be determined inaccordance with the setting of a characteristic point (mentioned later).Moreover, the predetermined area may be set so as to correspond to theposition of the supporter 440 (jaw holder, forehead rest, etc.; refer toFIG. 4A and FIG. 4B.) supporting the face of the subject or the vicinityposition thereof.

A detailed example of the process carried out by the image determinationpart 232 is explained. First, the image determination part 232 specifiesthe image region corresponding to the predetermined characteristic pointof the anterior eye part Ea from the photograph image. Thischaracteristic point may be the center of the pupil, the contour of thepupil, the center of the iris, the contour of the iris, the cornealapex, etc. The process of specifying the image region corresponding tothe characteristic point is carried out similarly to, for example, theprocess carried out by the characteristic position specifying part 2312.It should be noted that when the characteristic point and thecharacteristic part are the same, the specification result by thecharacteristic position specifying part 2312 may be used in the processcarried out by the image determination part 232.

Next, the image determination part 232 judges whether or not thespecified characteristic point is within the predetermined area of thephotograph image (the frame thereof). This process may be carried out bycomparing the coordinates corresponding to the predetermined area andthe coordinates of the characteristic point.

The image determination part 232 transmits this determination result tothe controller 210. When it is determined that the image of the anterioreye part Ea is not included in the predetermined area, the controller210 controls the optical system driver 2A (camera moving part) to movethe anterior eye cameras 300 in a direction away from the supporter 440(that is, the face of the subject) and/or a direction outwards of thesupporter 440. The direction away from the supporter 440 is the −zdirection in the coordinate system indicated in FIG. 1, etc. Moreover,the direction outwards of the supporter 440 is the direction in whichthe anterior eye cameras 300 moves away from the optical axis of theexamination optical system. The direction away from the examinationoptical system may be defined horizontally (±x direction) and/orvertically (±y direction). That is, the direction away from theexamination optical system may be defined in any direction in the xyplane.

Moreover, the moving direction and/or the moving distance of theanterior eye camera 300 may be set based on, for example, the positionalrelationship between the anterior eye camera 300 and the supporter 440before movement. Moreover, a configuration is possible of alternatelycarrying out the determination process by the image determination part232 and the moving process of the anterior eye camera 300, therebycontrolling so as to improve the position of the anterior eye camera 300toward a suitable position. Moreover, a configuration is possible ofdetermining the moving direction and/or the moving distance of theanterior eye camera 300 in accordance with the distance (number ofpixels) between the image region corresponding to the characteristicpoint and the predetermined area. Moreover, a configuration is possibleof determining the moving direction and/or the moving distance of theanterior eye camera 300 in accordance with the distance between theimage region corresponding to the characteristic point and thepredetermined position (for example, the center position) in thepredetermined area.

Other operation examples based on the determination result by the imagedetermination part 232 are explained. When it is determined that theimage of the anterior eye part Ea is not included in the predeterminedarea, the controller 210 causes an output part to output a predeterminedwarning information. This output part may be the display 241, an audiooutput part (not illustrated), etc. When using the display 241 as theoutput part, the controller 210 causes the display 241 to display awarning message including a predetermined text string information, imageinformation, pop-up window, etc. When the audio output part is used asthe output part, the controller 210 causes the audio output part tooutput the predetermined voice information, warning sound, etc.

From such warning information, the user recognizes that the image of theanterior eye part Ea is not included in the predetermined area.Subsequently, the user can use the operation part 242 tothree-dimensionally move the anterior eye camera 300. Further, thecontroller 210 may output information (movement information) indicatingthe moving direction and/or the moving distance of the anterior eyecamera 300 together with a warning information. This movementinformation is generated based on, for example, the positionalrelationship between the image region corresponding to thecharacteristic point obtained by the image determination part 232 andthe predetermined area. A configuration is possible wherein thedetermination process is carried out again by the image determinationpart 232 once the manual movement by the user is completed.

(Image Synthesis Part)

The image synthesis part 233 forms a synthetic image of the two or morephotograph images that are substantially and simultaneously obtained bytwo or more anterior eye cameras 300. A stereoscopic image and an imageobtained from viewpoint conversion (viewpoint-converted image) based onthe two or more photograph images are examples of the synthetic image.The viewpoint of the viewpoint-converted image is set on, for example,the optical axis of the examination optical system. These syntheticimages may be obtained by using any known image synthesizing process.

The image processor 230 that functions as above includes, for example,the aforementioned microprocessor, RAM, ROM, hard disk drive, circuitboard, and so on. Computer programs that cause a microprocessor toexecute the above functions are previously stored in a storage devicesuch as a hard disk drive.

(User Interface)

A user interface 240 includes the display 241 and the operation part242. The display 241 is configured including the aforementioned displaydevice of the arithmetic and control unit 200 and the display device 3.The operation part 242 is configured including the aforementionedoperation device of the arithmetic and control unit 200. The operationpart 242 may include various kinds of buttons or keys provided on thecase of the ophthalmologic apparatus 1 or its outside. For example, ifthe retinal camera unit 2 has a case that is the similar to conventionalretinal cameras, a joy stick, operation panel, etc. provided on thiscase may be included in the operation part 242. Furthermore, the display241 may include various display devices such as a touch panel, etc.provided on the case of the retinal camera unit 2.

It should be noted that the display 241 and the operation part 242 donot need to be configured as separate devices. For example, like a touchpanel, a device in which the display function and the operation functionare integrated can be used. In such cases, the operation part 242 isconfigured to include this touch panel and a computer program. Thecontent of operation via the operation part 242 is input to thecontroller 210 as an electric signal. Moreover, operations and inputs ofinformation may be performed by using a graphical user interface (GUI)displayed on the display 241 and the operation part 242.

[Operations]

Operations of the ophthalmologic apparatus 1 are described below.

Operation Example 1

This operation example explains the fundamental flow of automaticalignment by the ophthalmologic apparatus 1 and the processes that arecarried out in the event of failure in specifying the characteristicpart of the anterior eye part Ea (here, the center of the pupil) or whenthe image of the anterior eye part Ea is not included in thepredetermined area of a photograph image. Now, the flowchart shown inFIG. 6 is referred to.

(S1: Patient registration)

First, the user inputs patient information on a subject using the userinterface 240. The patient information may be a patient ID, patientname, etc.

(S2: Selection of Photography Type)

Next, the user uses the user interface 240 to select and input the typeof photography carried out with respect to the subject. The items of thephotography type may include, for example, a photographing site (opticpapilla, macula, or both, etc.), the photographed eye (left eye, righteye, both eyes), image photographing pattern (only a fundus image, onlyan OCT image, or both), OCT scanning pattern (line scan, cross scan,radial scan, circle scan, three-dimensional scan, etc.)

(S3: Commencement of Automatic Alignment)

Once the selection of the photography type is completed, an instructionfor commencing automatic alignment is given. This commencementinstruction may be automatically given by the controller 210 uponreceiving the selection of the photography type or may be manually givenby the user using the operation part 242.

(S4: Commencement of Photography of Anterior Eye Part)

Once the instruction for commencing automatic alignment is given, thecontroller 210 causes the respective anterior eye cameras 300A and 300Bto commence photographing of the anterior eye part Ea. Thisphotographing is moving image photography of the anterior eye part Ea asthe photography subject. The respective anterior eye cameras 300A and300B carry out moving image photography at a predetermined frame rate.Here, the timings of photographing by the anterior eye cameras 300A and300B may be synchronized by the controller 210. The respective anterioreye cameras 300A and 300B successively transmit the acquired frames tothe controller 210 in real time. The controller 210 associates theframes obtained by both anterior eye cameras 300A and 300B in accordancewith the photography timing. That is, the controller 210 associates theframes substantially and simultaneously acquired by both anterior eyecameras 300A and 300B with each other. This association is carried outbased on, for example, the abovementioned synchronous control or basedon the input timings of the frames from the anterior eye cameras 300Aand 300B. The controller 210 transmits the pair of the associated framesto the analyzer 231.

(S5: Specification of the Center of the Pupil)

The image correction part 2311 corrects the distortion of each frametransmitted from the controller 210 based on the aberration information212 a stored in the storage 212. This correcting process is carried outin the abovementioned manner. The pair of frames with the distortionthereof corrected is transmitted to the characteristic positionspecifying part 2312.

The characteristic position specifying part 2312 analyzes each frametransmitted from the image correction part 2311, thereby carrying outthe process for specifying the characteristic position in the framecorresponding to the center of the pupil of the anterior eye part Ea.

(S6: Has the Specification of the Center of the Pupil Succeeded?)

In the event of failure in specifying the characteristic positioncorresponding to the center of the pupil (S6: NO), the characteristicposition specifying part 2312 transmits the information indicating thisresult to the controller 210, and the process is transferred to “Movingthe anterior eye camera” of Step S7. On the other hand, if specificationof the center of the pupil has been successful (S6: YES), it shifts to“Is the image of the anterior eye part positioned within a predeterminedarea of the frame?” of Step S8.

(S7: Moving the Anterior Eye Camera)

In the event of failure in specifying the characteristic position (S6:NO), the controller 210, in response to reception of the informationfrom the characteristic position specifying part 2312, controls thecamera moving part mentioned above to move the anterior eye cameras 300Aand 300B in the direction away from the supporter 440 and/or thedirection outwards of the supporter 440.

In the event of moving the anterior eye cameras 300A and 300B in thedirection away from the supporter 440, the distance between the anterioreye cameras 300A and 300B and the subject (the eye E) increases;thereby, it becomes possible to photograph a wider scope of thesubject's face, increasing the possibility of the eye E being positionedin a range suitable for photographing by the anterior eye cameras 300Aand 300B. Moreover, in the event of moving the anterior eye cameras 300Aand 300B in the direction outwards of the supporter 440, the anterioreye cameras 300A and 300B move in the direction of the subject's ear,increasing the possibility of the eye E being positioned in a rangesuitable for photographing by the anterior eye cameras 300A and 300B.Moreover, by combining the movement in these two directions, thepossibility of the eye E being positioned in a range suitable forphotographing is further enhanced.

In this operation example, it is regarded that the moving imagephotography of the anterior eye part Ea is continued even while movingor after moving the anterior eye cameras 300A and 300B. Instead, it ispossible to stop the moving image photography upon moving the anterioreye cameras 300A and 300B and automatically or manually re-starting themoving image photography after the moving is completed.

After completion of moving the anterior eye cameras 300A and 300B,moving image photography by the anterior eye cameras 300A and 300B,specification of the center of the pupil, and determination forsuccessful specification are carried out again. It should be noted thata configuration is possible of transferring to manual alignment whenthis routine is repeated a predetermined number of times.

(S8: Is the Image of the Anterior Eye Part Positioned within aPredetermined Area of the Frame?)

Upon successful specification of the characteristic positioncorresponding to the center of the pupil (S6: YES), the imagedetermination part 232 determines whether or not the image correspondingto the anterior eye part Ea is within a predetermined area of the frame.In this operation example, this determination process is carried outusing the characteristic position specified by the characteristicposition specifying part 2312. Instead, when using other information tocarry out the determination process, the abovementioned processes may bein any order.

In the event a determination is made that the image of the anterior eyepart Ea is not positioned within a predetermined area of the frame (S8:NO), the anterior eye cameras 300A and 300B are moved again (S7). On theother hand, in the event a determination is made that the image of theanterior eye part Ea is positioned within a predetermined area of theframe (S8: YES), it goes to “Calculating the three-dimensional positionof the eye” of the next step (S9).

(S9: Calculating the Three-Dimensional Position of the Eye)

The three-dimensional position calculating part 2313 calculates thethree-dimensional position of the center of the pupil of the eye E basedon the positions of the anterior eye cameras 300A and 300B and thecharacteristic position specified by the characteristic positionspecifying part 2312 regarding the pair of frames. This process iscarried out in the abovementioned manner.

(S10: Moving the Examination Optical System)

Based on the three-dimensional position of the center of the pupilcalculated by the three-dimensional position calculating part 2313 inStep S9, the controller 210 controls the optical system driver 2A so asto match the optical axis of the examination optical system with theaxis of the eye E, and such that the distance of the examination opticalsystem with respect to the eye E becomes the specific working distance.

(S11: Is the Position Converged?)

When the examination optical system is moved, the controller 210determines whether or not the position of the examination optical systemhas converged. This determination process is carried out by, forexample, using the alignment target. The observation condition of thealignment target changes depending on the alignment state. Specifically,when the alignment is in a suitable state, two images of the alignmenttarget are observed in substantially the same position, while the morethe alignment state worsen, the more the two images are observed apartfrom each other. The controller 210 obtains the distance between thesetwo images photographed by the CCD image sensor 35, and determineswhether or not this distance is within a specific threshold or less.When a determination is made that the distance is equal to the specificthreshold or less, it is determined that the position of the examinationoptical system is converged, completing the process (S11: YES).

Whereas, when a determination is made that this distance exceeds thespecific threshold, it is determined that the position of theexamination optical system is not converged, returning to the process“Calculating the three-dimensional position of the eye” of Step 9 (S11:NO). The processes from “Calculating the three-dimensional position ofthe eye” of Step 9 to Step 11 are repeated until, for example,determined as “NO” in Step 11 a specific number of times. In the eventthe determination of “NO” is repeated the specific number of times, thecontroller 210 outputs, for example, a specific warning information.Moreover, in correspondence with the determination of “NO” beingrepeated the specific number of times, the controller 210 may executecontrol of transferring to an operation mode for carrying out manualalignment or an operation mode for automatic alignment using thealignment target.

It should be noted that such position convergence determination processis not limited to this; however, any method is possible as long as theprocess is capable of determining whether or not the position of theexamination optical system is appropriately converged. This concludesthe explanation of the automatic alignment according to this operationexample.

Operation Example 2

This operation example explains the operation of the ophthalmologicapparatus 1 applicable when there is a danger of the eye having anegative influence on light irradiated onto the fundus, such as the casein which the eye has a cataract. Moreover, this operation exampleexplains a new alignment method and a new method of representingalignment state regarding an ophthalmologic apparatus, and it alsoexplains, regarding an ophthalmologic apparatus for imaging a fundususing OCT, a technology that is capable of suitably acquiring a frontimage of a fundus even when the pupil of the eye is small.

The automatic alignment explained in Operation example 1 above involvesautomatically carrying out alignment with respect to the center of thepupil of the eye; however, when the crystalline lens is opaque, forexample, due to cataracts, signal light becomes scattered by the opaqueportion, thereby preventing effective OCT images from being acquired.Under such conditions, in this operation example, alignment is performedwith respect to the position dislocated from the center of the pupil,thereby carrying out OCT measurement by avoiding the opaque portion.

An example of a process flow of this operation example is shown in FIG.7A and FIG. 7B. Further, examples of displayed screens in this operationexample are shown in FIG. 8A to FIG. 8I. Here, it is assumed that thepatient registration (S1) and the selection of the photography type (S2)in Operation example 1 have already been carried out, and that theimaging by the anterior eye cameras 300 has already been started (S4).

(S21: Displaying an Imaging Screen)

The controller 210 controls the display 241 to display an imaging screen1000 shown in FIG. 8A. In the display region (first display region) 1001on the left hand side in the imaging screen 1000, an infraredobservation image (a front image of the anterior eye part Ea) 2000acquired by the retinal camera unit 2 is displayed in real time as amoving image. Further, in the display region (second display region)1002 on the right hand side in the imaging screen 1000, an anterior eyeimage acquired by one of the anterior eye cameras 300A and 300B isdisplayed as a moving image. A “Capture START” button 1003 is providedbelow the second display region.

(S22: Automatic Alignment)

Upon receiving the operation (click operation) to the “Capture START”button 1003, the controller 210 controls the display 241 to display analignment screen 1010 for executing automatic alignment (see FIG. 8B).At least an image used for carrying out the automatic alignment isdisplayed in the alignment screen 1010.

The automatic alignment is carried out, for example, in the manner asexplained in Operation example 1. Alternatively, it is also possible tocarry out the automatic alignment based on a pair of anterior eye imagesacquired by the anterior eye cameras 300A and 300B.

An example of the automatic alignment using a pair of anterior eyeimages acquired by the anterior eye cameras 300A and 300B is explained.In the present example, two anterior eye images of the eye E acquired bythe anterior eye cameras 300A and 300B are synthetically displayed.These anterior eye images are respectively acquired in real time, andthe synthetic image (composed image) of them is displayed as a movingimage in real time. That is, this synthetic display is a moving imagedisplay in which a synthetic image (still image) based on the twoanterior eye images (still images) substantially simultaneously acquiredby the anterior eye cameras 300A and 300B is regarded as a single frame.

A method or creating each frame (each synthetic image) is explained. Asmentioned above, a single frame is based on the anterior eye imagessubstantially simultaneously acquired by the anterior eye cameras 300Aand 300B.

As the first example of forming a frame, it is possible to display apartial image of one anterior eye image and a partial image of anotheranterior eye image in parallel. For these partial images, partsdiffering from each other are used in the original frames.

A first display region 1011 and a second display region 1012 areprovided in the alignment screen 1010 shown in FIG. 8B. In the firstdisplay region 1011, a first partial image 2110 corresponding to theupper half of the frame of the anterior eye image acquired by theanterior eye camera 300A is displayed. In the second display region1012, a second partial image 2120 corresponding to the bottom half ofthe frame of the anterior eye image acquired by the eye camera 300B isdisplayed. The first display region 1011 and the second display region1012 are arranged such that the former is in the upper position and thelatter is in the lower position. Here, the lower side of the firstdisplay region 1011 and the upper side of the second display region 1012are in contact.

When the retinal camera unit 2 is moved in the ±z-direction by theoptical system driver 2A, along with the change in positions of theanterior eye cameras 300A and 300B with respect to the eye E, the twopartial images 2110 and 2120 are relatively and transversely displacedeach other. Moreover, when the retinal camera unit 2 is moved in thexy-direction by the optical system driver 2A, along with the change inpositions of the anterior eye cameras 300A and 300B with respect to theeye E, the two partial images 2110 and 2120 are integrally displacedwithin the respective display regions 1011 and 1012 in a direction inaccordance with the moving direction of the optical system of theapparatus.

As explained above, the analyzer 231 analyzes the first partial image2110 (or the whole original image thereof) to specify the image regioncorresponding to the characteristic site of the eye E (firstcharacteristic region). Similarly, the analyzer 231 analyzes the secondpartial image 2120 (or the whole original image thereof) to specify theimage region corresponding to the characteristic site of the eye E(second characteristic region). Each of the characteristic sites is, forexample, a pupil (the outline of the pupil or the center of the pupil).In FIG. 8B, the symbol 2110 a indicates a first characteristic regioncorresponding to the outline of the pupil, and the symbol 2120 aindicates a second characteristic region corresponding to the outline ofthe pupil.

Moreover, the analyzer 231 calculates the displacement between the firstcharacteristic region 2110 a and the second characteristic region 2120a. This displacement includes the displacement in the lateral direction.As described above, the lateral displacement corresponds to thepositional gap of the examination optical system in the ±z-direction.The analyzer 231 obtains the moving direction and the moving distance ofthe examination optical system that correspond to the displacementbetween the first characteristic region 2110 a and the secondcharacteristic region 2120 a calculated by itself. This process iscarried out by, for example, referring to information associatingdisplacements between characteristic regions with moving directions andmoving distances. This information is created in advance based on thelocations of the two anterior eye cameras 300A and 300B and/or workingdistance, and stored in the storage 212 or the analyzer 231.

The controller 210 controls the optical system driver 2A based on themoving direction and the moving distance obtained by the analyzer 231 tomove the retinal camera unit 2 in the +z-direction or −z-direction. Byperforming such processes, alignment in the z-direction is carried outsuch that the first characteristic region 2110 a and the secondcharacteristic region 2120 a match each other (that is, the combinationof the first characteristic region 2110 a and the second characteristicregion 2120 a forms an image depicting the pupil) (see FIG. 8C).

The parenthesis 2101 represented in substantially the center of thescreen and the circle 2102 surrounded by this parenthesis illustrated inFIG. 8C indicates the target position for alignment. The parenthesis2101 shows a target position of the outline of the pupil, and the circle2102 shows a target position of the center of the pupil.

Further, the analyzer 231 calculates the displacement of the respectivepositions of the first characteristic region 2110 a and the secondcharacteristic region 2120 a and the target position (the parenthesis2101, the circle 2102). Moreover, the analyzer 231 derives the movingdirection and the moving distance of the examination optical systemcorresponding to the displacement calculated by itself. This process iscarried out by, for example, referring to information associatingdisplacements between characteristic regions and target positions withmoving directions and moving distances. This information is created inadvance based on the locations of the two anterior eye cameras 300A and300B and/or working distance, and stored in the storage 212 or theanalyzer 231.

The controller 210 controls the optical system driver 2A based on themoving direction and the moving distance obtained by the analyzer 231 tomove the retinal camera unit 2 in the +x-direction or −x-directionand/or in the +y-direction or −y-direction. By performing suchprocesses, alignment in the xy-direction is carried out. By adjustingboth the alignment state in the xy-direction and the alignment state inthe z-direction, the examination optical system is located in thesuitable three-dimensional position with respect to the eye E. At thistime, the alignment screen 1010 is in the display state illustrated inFIG. 8C.

As a second example of preparing a frame, at least part of one anterioreye image may be overlaid on at least part of the other anterior eyeimage. This overlay is carried out by using, for example, a layeringfunction. The opacity of the front layer is set beforehand to a specificvalue allowing visual contact of the image on the rear layer. In thepresent example as well, the alignment screen 1010 illustrated in FIGS.8B and 8C is displayed, and alignment in the z direction and alignmentin the xy-direction are carried out in the same manner as the firstexample. The displacement of the images regarding these alignments isalso the same as in the first example.

The “Capture STOP” button 1013 shown in FIG. 8B and FIG. 8C is operated(clicked) for stopping (or suspending) the process of this operationexample.

(S23: Automatic Focusing)

Upon receiving the completion of the automatic alignment, the controller210 carries out automatic focusing using the split target in the waydescribed above.

(S23: Automatic Focus)

Upon receiving the completion of the automatic focusing, the controller210 controls the display 241 to display the Auto-Z screen 1020 shown inFIG. 8D, and starts Auto-Z. It should be noted that the configuration isalso possible in which Auto-Z is started in response to prescribedtrigger (for example, the instruction by the user).

(S24: Auto-Z)

In the Auto-Z screen 1020, the synthetic image (an image obtained bycomposing two anterior eye images) 2130 similar to that in the alignmentscreen 1010 of FIG. 8C is displayed. The display mode of this syntheticimage 2130 is, for example, movie display; however, it may be a stillimage display. The synthetic image 2130 is, for example, displayed inthe upper right region of the Auto-Z screen 1020.

The OCT image display part 1021 for displaying OCT images is providedbelow the synthetic image 2130. Further, the indicator 1022 forrepresenting prescribed evaluation value is provided below the OCT imagedisplay part 1021. This evaluation value may be a value indicating theimage quality of the image displayed in the OCT image display part 1021,or a value indicating the degree of success/failure of Auto-Z (e.g. avalue calculated based on the distance between the image correspondingto a prescribed tissue of the eye E and a target area in the frame). Theevaluation value is calculated by, for example, the analyzer 231analyzing an OCT image (cross sectional image). The controller 210displays the calculated evaluation value in the indicator 1022.

The front image 3000 of the fundus Ef is displayed on the left of thesynthetic image 2130 and the OCT image display part 1021. The frontimage 3000 may be an infrared observation image, an infraredphotographed image, or a color image. The infrared observation image isa real time moving image obtained by photographing the fundus Ef. Theinfrared photographed image and the color image are still imagesphotographed the fundus Ef in the past. It should be noted that it isalso possible to display a moving image obtained in the past as thefront image 3000. The front image 3000 is overlaid by the arrow markindicating a scanning position applied in OCT measurement. At least partof this mark may indicate a scanning position applied in Auto-Z. Theuser can arbitrarily change the position of the mark by using theoperation part 242. The controller 210 is capable of control the galvanoscanner 42 so as to perform scanning based on the position of the markafter the change.

(S25: Succeeded?)

When Auto-Z has succeeded in this stage (S25: YES), Step S38 of FIG. 7Bis carried out. Step S38 and the processes after this are describedlater.

(S26: Displaying a Dialog Box)

On the other hand, when Auto-Z has failed (S25: NO), the controller 210displays the dialog box 1030 as a pop-up display shown in FIG. 8E. Thedialog box 1030 is provided with a message “Could not detect image”indicating the failure of Auto-Z and software keys 1031 and 1032. Thesoftware key 1031 is a “Retry” button, and the software key 1032 is a“Search” button.

(S27: Retry/Search?)

When the “Retry” button 1031 is operated (clicked) (S27: Retry), theprocess is returned to Step S24 and Auto-Z is started again.

(S28: Moving the Optical System in the Inferior (Nasal) Direction)

On the other hand, when the “Search” button 1032 is operated (clicked)(S27: Search), the controller 210 controls the optical system driver 2Ato move the retinal camera unit 2 in the predetermined direction bypredetermined distance. Thereby, the position of the examination opticalsystem relative to the eye E is changed in the predetermined directionby predetermined distance.

Further, the controller 210 displays a dialog box indicating themovement state of the examination optical system as a pop-up display.The dialog box 1040 shown in FIG. 8F is an example of the dialog boxdisplayed when the examination optical system is moved to lowerposition.

The movement direction of the examination optical system is set in thedirection perpendicular to the OCT scanning direction in Auto-Z. This isbased on the fact that when the examination optical system is moved inthe scanning direction, the optical path length of the signal light inthe eye, thereby the position of the image of the eye depicted in theframe is shifted in the vertical direction.

Examples of the movement direction of the examination optical system areillustrated in FIG. 9A and FIG. 9B. As shown in FIG. 9A, when thehorizontal line scanning (horizontal scanning) L1 is applied in Auto-Z,it is possible to move the examination optical system in the directionperpendicular to the horizontal scanning L1 (that is, the upwarddirection M11 or the downward direction M12) in Step S28.

It should be noted that when the subject is an aged person, the uppereyelid is nutated and positioned just in front of the pupil. Consideringsuch situation, when the horizontal scanning L1 is applied in Auto-Z, itis to be desired that the examination optical system is moved in thedownward direction M12.

Further, when the vertical line scanning (vertical scanning) L2 isapplied in Auto-Z as shown in FIG. 9B, it is possible to move theexamination optical system in the direction perpendicular to thevertical scanning L2 (that is, the leftward direction M21 or therightward direction M22) in Step S28.

When the eye E is a left eye, the leftward direction M21 corresponds tothe ear side, and the rightward direction M22 corresponds to the noseside. On the other hand, when the eye E is a right eye, the leftwarddirection M21 corresponds to the nose side, and the rightward directionM22 corresponds to the ear side. In general, the directions in thefundus Ef is expressed by the upward direction (superior), the downward(inferior), the nose side (nasal), and the ear side (temporal). Here,vertical direction is set along the midline (sagittal line) of thesubject, the “nasal” corresponds to the direction getting closer to thesagittal line along the direction perpendicular to the sagittal line,and the “temporal” corresponds the direction getting going away from thesagittal line along the direction perpendicular to the sagittal line.That is, the line indicating the superior-inferior direction and theline indicating the nasal-temporal direction are perpendicular to eachother.

In this operation example, when the vertical scanning L2 is applied inAuto-Z, the examination optical system is controlled to move in thenasal direction. It should be noted that the movement direction of theexamination optical system in this stage may be arbitrary (that is, maybe the superior direction, the temporal direction, or an obliquedirection).

FIG. 10 illustrates an example of the movement direction of theexamination optical system in the case in which various scanningpatterns can be applied. Here, “3D” indicates three-dimensional scan,“Radial” indicates radial scan, and “Line” indicates line scan. Further,“5LineCross” indicates a scan pattern combining five parallel line scansin vertical direction and five parallel line scans in horizontaldirection. Moreover, “Macula” indicates that the imaging target is amacula, while “Disc” indicates that the imaging target is an opticpapilla. Moreover, “Wide” refers to scanning a wide range, while “H”indicates the horizontal direction and “V” indicates the verticaldirection. The information illustrated in FIG. 10 is stored in thestorage 212 in advance. The controller 210 may obtain the movementdirection corresponding to the scanning pattern applied, and control theoptical system driver 2A so as to move the examination optical system inthe movement direction obtained.

Next, the movement distance of the examination optical system isexplained. The movement distance is, for example, as indicated in FIG.10, determined from the diameter of the minimal pupil region D0 to whichOCT measurement can be applied (minimal pupil diameter) “2*r0” (forexample, 2.5 mm), and the diameter of the beam cross-section D1 of thesignal light (beam diameter) “2*r1” (for example, 1.1 mm). The maximummovement distance is the half of the difference between the minimalpupil diameter and the beam diameter: r=r0−r1. It should be noted thatthe movement distance of the examination optical system in Step S28 maybe the maximum movement distance calculated in this manner (0.7 mm), ormay be shorter distance. That is, the movement distance of theexamination optical system may be arbitrary set within a range in whichsignal light is not irradiated to the iris that shaping the pupil. Forexample, it is possible to stepwise move the alignment position in thisrange.

(S29: Auto-Z)

In response to the completion of the movement of the examination opticalsystem, the controller 210 carries out Auto-Z again.

(S30: Succeeded?)

When Auto-Z has succeeded in this stage (S30: YES), Step S38 of FIG. 7Bis carried out. Step S38 and the processes after this are describedlater. On the other hand, when Auto-Z has failed in this stage (S30:NO), Step S31 of FIG. 7B is carried out.

(S31: Moving the Examination Optical System in the Superior (Temporal)Direction)

When Auto-Z has failed in Step S30 (S30: NO), the controller 210controls the optical system driver 2A to move the retinal camera unit 2in the opposite direction to that in Step S28. For example, when theexamination optical system is moved in the inferior (or nasal) directionin Step S28, the examination optical system is moved in the superior (ortemporal) direction in Step S31.

Further, the movement distance in Step S31 is set, for example, thedouble of the movement distance in Step S28. In this case, the opticalaxis of the examination optical system is moved to the positionpredetermined distance (e.g. 0.7 mm) away from the initial position (thecenter of the pupil) in the inferior (or nasal) direction in Step S28,and then, moved to the position predetermined distance (e.g. 0.7 mm)away from the initial position in the superior (or temporal) directionin Step S31.

Further, the controller 210 displays a dialog box indicating themovement state of the examination optical system as a pop-up display.The dialog box 1050 shown in FIG. 8G is an example of the dialog boxdisplayed when the examination optical system is moved to upperposition.

(S32: Auto-Z)

In response to the completion of the movement of the examination opticalsystem, the controller 210 carries out Auto-Z again.

(S33: Succeeded?)

When Auto-Z has succeeded in this stage (S33: YES), Step S38 of FIG. 7Bis carried out. Step S38 and the processes after this are describedlater.

(S34: Displaying a Dialog Box)

When Auto-Z has failed in Step S33 (S33: NO), the controller 210displays the dialog box 1060 shown in FIG. 8H as a pop-up display. Thedialog box 1060 is provided with a message “Could not detect image.Search image manually” indicating the failure of (the final) Auto-Z andprompting to transfer manual adjustment. Further, the dialog box 1060 isprovided with the “OK” button 1061.

(S35: Transferring to the Manual Mode)

Upon receiving the operation of the “OK” button 1061, the controller 210displays the manual mode screen 1100 shown in FIG. 8I. The manual modescreen 1100 is used for manual alignment, and for manually performingprocesses to depict the image of the fundus Ef within the target area inthe frame.

Images and software keys for carrying out the above processes arerepresented in the manual mode screen 1100. Specifically, the syntheticimage 2130 of the anterior eye part Ea and the front image 3000 of thefundus Ef are displayed in the manual mode screen 1100. Further, themanual mode screen 1100 is provided with the OCT image display part1101. OCT images acquired in real time and/or OCT images acquired in thepast are displayed in the OCT image display part 1101. The measurementdepth marker 1102 is provided in the right end part of the OCT imagedisplay part 1101. The measurement depth marker 1102 is described later.

The indicator 1103 for presenting a predetermined evaluation value isprovided below the OCT image display part 1101. The evaluation valuerepresents the image quality of the image displayed in the OCT imagedisplay part 1101, and it is calculated by the analyzer 231 analyzing anOCT image (cross sectional image). The controller 210 displays theevaluation value calculated in the indicator 1103.

An example of the operation mode using the manual mode screen 1100. Thearrow buttons for moving the acquiring position of the front imagetwo-dimensionally is provided in the upper end, the lower end, the leftend and the right end of the front image 3000. When any one of the arrowbuttons is operated, the controller 210 controls the optical systemdriver 2A to move the examination optical system in the direction(xy-direction) corresponding to this arrow button.

An arrow mark indicating the scanning position of the signal light isdisplayed over the front image 3000. The user moves the mark byoperating the arrow buttons, thereby being capable of arbitrarily changethe scanning position. The movement of the scanning position isreflected to the control of the galvano scanner 42.

A pair of rotation buttons (arc-shaped arrow mark) is provided in theupper right position of the front image 3000. The user operates theserotation buttons to arbitrarily rotate the scanning position. Therotation of the scanning position is reflected to the control of thegalvano scanner 42.

The measurement depth marker 1102 arranged in the right end part of theOCT image display part 1101 is moved in the vertical direction by clickoperations and/or drag operations using the operation part 242. Thecontroller 210 carries out control of the optical-path-length changingpart 41 in accordance with the position of the measurement depth marker1102. Thereby, the measurement depth of OCT is changed. In other words,the depiction position of the image of the fundus Ef in the frame ismoved in the z-direction.

The “Optimize” button for automatically carrying out the image qualityoptimization and the “Manual” button for manually carrying out the imagequality optimization are provided in the OCT image display part 1101.The image quality optimization includes a process for adjusting thedifference of the optical path length of the signal light and theoptical path length of the reference light.

Software keys for carrying out various operations are provided in thelower left part of the front image 3000. The software keys are used formoving the internal fixation target projected by LCD 39 to a defaultposition and moving the projection position of the internal fixationtarget in the vertical and horizontal directions.

Further, for example, the following software keys are provided in themanual mode screen 1100: software keys for moving the examinationoptical system in the front-back direction (the z-direction), thehorizontal direction (x-direction) and the vertical direction(y-direction); software keys for carrying out focus adjustment; softwarekeys for changing the types of the fixation target; software keys forturning on/off an external fixation target (illustration omitted);software keys for change the operation mode to the microcoria mode (thatis, for inserting a microcoria diaphragm in the optical path).

(S36: Moving the Optical System to the Initial Position)

In response to transition to the manual mode, the controller 210controls the optical system driver 2A to move the examination opticalsystem to the initial position. The initial position is the position ofthe examination optical system before Step S28, and specifically, itcorresponds to the position in which the examination optical system ismatched with the center of the pupil, which is achieved by the automaticalignment (S22). The processes in Step S36 may include any of thefollowing; (1) the examination optical system is return to the positionobtained in Step S22; (2) new automatic alignment is carried out.

(S37: Manual Adjustment)

The user performs alignment, focusing, and a process for depicting theimage of the fundus Ef within the target area in the frame. Aftercompleting the manual adjustment, the user operates (clicks) the“Capture OK” button provided in the lower right part of the manual modescreen 1100.

(S38: Automatic Pola)

When Auto-Z in Step S24 has succeeded (S25: NO), when Auto-Z in Step S29has succeeded (S30: NO), when Auto-Z in Step S32 has succeeded (S33:NO), or when the “Capture OK” button is operated in Step S37, thecontroller 210 carries out automatic polarization adjustment (automaticPola). The automatic Pola is carried out by, for example, controllingthe polarization adjuster 106 while evaluating, in real time, the imagequality of OCT images (cross sectional images) repeatedly acquired.

(S39: OCT Automatic Focusing)

After the completion of automatic Pola, the controller 210 carries outOCT automatic focusing. The OCT automatic focusing is a process tochange the optical path length of the signal light by controlling theoptical-path-length changing part 41 so as to optimize the interferencesensitivity of the signal corresponding to a prescribed site of thefundus Ef (for example, any layer of the retina, or choroid).

(S40: Instruction to Start the Measurement)

After the completion of OCT automatic focusing, the controller 210controls the display 241 to display information showing this fact(illustration omitted). The user performs a trigger operation forstarting the measurement of the fundus Ef by using the operation part242.

It is also possible to apply a configuration in which the completion ofOCT automatic focusing is used as the trigger for starting themeasurement. In this case, Step S40 is not necessary.

(S41: OCT Measurement)

Upon receiving the trigger for starting the measurement, the controller210 causes the OCT unit 100 to carry out the OCT measurement of thefundus Ef. The image forming part 220 forms an OCT image based on thedetection signals from the OCT unit 100. The controller 210 stores theOCT image formed in the storage 212. When three-dimensional scan isapplied, the image processor 230 forms three-dimensional image databased on multiple cross sectional images formed by the image formingpart 220. The controller 210 stores the three-dimensional image dataformed in the storage 212.

(S42: Photographing the Fundus)

Upon receiving the completion of the OCT measurement, the controller 210causes the retinal camera unit 2 to photograph the fundus Ef. The imagedata obtained by the retinal camera unit 2 is stored in the storage 212by the controller 210. This is the end of the explanation of thisoperation example.

[Effects]

The effects of the ophthalmologic apparatus according to the presentembodiment are explained.

the ophthalmologic apparatus according to the present embodimentincludes an examination part, a moving mechanism, an informationobtaining part, and a controller.

The examination part includes an optical system for optically examiningan eye. This examination includes, for example, OCT measurement. Theexamination part includes, for example, the retinal camera unit 2 andthe OCT unit 100 of the above embodiment. The moving mechanism moves theoptical system. The moving mechanism includes, for example, the opticalsystem driver 2A of the above embodiment.

The information obtaining part obtains information for carrying outposition matching of the optical system to the eye (for example, theautomatic alignment of Step S22). The information obtaining partincludes, for example, at least one of the anterior eye cameras 300 andthe retinal camera unit 2 of the above embodiment.

The controller carries out first control for the moving mechanism basedon the information obtained by the information obtaining part to movethe optical system (for example, the automatic alignment of Step S22).Further, the controller determines whether information opticallyobtained by the optical system after the first control is appropriate tothe examination or not (for example, the Auto-Z of Step S24 and thedetermination process of Step S25). When it is determined that thisinformation is not appropriate, the controller carries out secondcontrol for the moving mechanism in response to a prescribed trigger(for example, the selection of “Search” in Step S27) to move the opticalsystem (for example, the movement process of Step S28). The controllerincludes, for example, the controller 210, the image forming part 220and image processor 230 of the above embodiment.

According to the ophthalmologic apparatus with such configurations, thefollowing effect can be provided. The ophthalmologic apparatus iscapable of judging whether or not there is a factor that disturbs light(for example, an opaque portion) in the eye by the determination processexecuted after the first control. When there is a disturbing factor, theophthalmologic apparatus can move the optical system by the secondcontrol so as to avoid the disturbing factor. Therefore, According tothe ophthalmologic apparatus of the embodiment, it is possible to carryout examinations even when there is a factor that disturbs light in aneye.

In the embodiment, the controller may be configured to carry out thefollowing processes (1) and (2).

(1) The controller determines whether information optically obtained bythe optical system after the second control is appropriate to theexamination or not (for example, the Auto-Z of Step S29 and thedetermination process of Step S30). This determination process may becarried out in the similar way as the determination process after thefirst control.(2) When it is determined that this information is not appropriate, thecontroller carries out third control for the moving mechanism to movethe optical system (for example, the movement process of Step S31).

According to this configuration, when the disturbing factor stillprevents the examination after the second control, it is possible tomove the optical system again. Therefore, examinations can be carriedout even when there is a factor that disturbs light in an eye.

In the embodiment, the controller may be configured to move the opticalsystem in a first direction by the second control, and move the opticalsystem in a second direction that is the opposite direction to the firstdirection by the third control. Further, the controller may beconfigured to move, by the second control, the optical system to theposition that is prescribed distance away in the first direction fromthe position after the movement by the first control, and move, by thethird control, the optical system to the position that is the prescribeddistance away in the second direction from the position after themovement by the first control. According to such configurations, whenthe position of the optical system after the movement in the firstdirection is not appropriate, the optical system is moved in the seconddirection that is the opposite direction thereof, consequently, it ispossible to enhance the possibility of being able to carry out theexamination while avoiding the opaque portion etc. as a disturbingfactor.

In the embodiment, the first direction, which is the movement directionof the optical system by the second control, may be a downward directionor a sagittal line direction (nasal direction). In this case, the seconddirection, which is the movement direction of the optical system by thethird control, may be an upward direction or a direction apart from thesagittal line (temporal direction). According to such configurations,even when the upper eyelid is nutated, or even when the eyelashes of theupper eyelid are positioned just in front of the pupil, it is possibleto smoothly carry out the examination. It should be noted that opacitydue to cataract is a typical example of the disturbing factor. Theopacity due to cataract is often found for aged persons, and the descentof the eyelid is also often found for aged persons. Consequently, thisconfiguration is effective in examinations for aged persons.

The following configuration may be applied to the embodiment. First, theoptical system is configured to irradiate light from a light source (forexample, the observation light source 11 or the light source unit 101)onto an eye fundus, and detect returned light of this light from the eyefundus. Further, the controller is configured to perform the abovepropriety determination based on the detection result of the returnedlight.

Specific examples of such a configuration include the followingconfiguration. First, the optical system is configured to split lightfrom the light source (for example, the light source unit 101) intosignal light and reference light, scan the eye fundus with the signallight, and detect interference light obtained by composing returnedlight of the signal light from the eye fundus and the reference light.That is, this optical system is an interferometer for OCT measurement.Further, the examination part is configured to include a cross sectionalimage forming part (for example, the image forming part 220 (and theimage processor 230)) configured to form a cross sectional image of theeye fundus based on the detection result of the interference light bythe optical system. That is, this ophthalmologic apparatus functions asan OCT apparatus for imaging the eye fundus. Moreover, the controller isconfigured to carry out the above propriety determination based on thedetection result of the interference light or the cross sectional image.This configuration is one that performs the above proprietydetermination based on the interference signals obtained by OCTmeasurement or based on an OCT image formed from the interferencesignals.

Such propriety determination based on OCT measurement may includedetermination of success/failure of Auto-Z. In this case, the followingconfiguration may be applied. First, the optical system is configured toinclude an optical-path-length changing part (for example, theoptical-path-length changing part 41) configured for relatively changingoptical path length of the signal light and optical path length of thereference light. Further, the controller is configured to carry out thefollowing processes in the determination. The controller controls theoptical system in such a way as to repeatedly scan the same portion ofthe eye fundus, and, at the same time, controls the optical-path-lengthchanging part such that the eye fundus is depicted in a prescribed areain a frame based on detection results of the interference light or crosssectional images repeatedly obtained by this control. This processcorresponds to Auto-Z. When the eye fundus is not depicted in theprescribed area by the Auto-Z, the controller determines that theinformation optically obtained by the optical system is not appropriate.

It should be noted that the propriety determination may be carried outbased on a process other than Auto-Z. For example, the proprietydetermination may be carried out based on the intensity of aninterference signal, the amount of noises in an interference signal, theimage quality of a cross sectional image, or the amount of noises in across sectional image.

As described above, when the result “not appropriate” is obtained in thepropriety determination, the controller carries out the second controlfor the moving mechanism in response to the prescribed trigger. In theembodiment, the “prescribed trigger” may be the following operations.First, the controller is configured to display an object including afirst operating element on a display means (for example, the display241) in response to the acquisition of the determination result “notappropriate” in the propriety determination after the first control.This object is, for example, the dialog box 1030 displayed in Step S26(see FIG. 8E). Further, the first operating element is, for example, the“Search” button 1032. The user perform an operation to the firstoperating element (for example, click operation) using an operatingmeans (for example, the operation part 242). This operation correspondsto the “prescribed trigger”. According to this configuration, it ispossible to execute the second control (that is, the control of movingthe alignment position) in accordance with the user's request.

In the case of displaying such objects, the following configuration maybe applied. First, the object includes a second operating element. Thesecond operating element is, for example, the “Retry” button 1031. Whenan operation to the second operating element is performed by using theoperating means, the controller carries out acquisition of informationby the optical system (for example, Auto-Z) again. According to thisconfiguration, it is possible for the user to select a desired processfrom among the movement of the alignment position, and the re-executionof the acquisition of information as well as the proprietydetermination.

In the embodiment, the first control (for example, the automaticalignment of Step S22) may be carried out as follows. First, theinformation obtaining part is provided with one or more imaging partconfigured to obtain a moving image of an anterior eye part of the eye.The imaging part includes, for example, the anterior eye camera 300and/or the retinal camera unit 2. Further, the controller is configuredto carry out the first control based on the moving image obtained by theimaging part.

In such configurations, it is possible to perform stereo photographingusing two imaging parts. For example, the information obtaining part isconfigured as follows. First, the information obtaining part includestwo imaging parts non-coaxially arranged to the optical system. The twoimaging parts are, for example, the anterior eye cameras 300A and 300B.It should be noted that the two imaging parts may be one of the anterioreye cameras 300A and 300B, and the retinal camera unit 2. Further, theinformation obtaining part includes a first displacement calculator (forexample, the analyzer 231) configured to calculate a displacementbetween the eye and the optical system by analyzing two imagessubstantially simultaneously obtained by the two imaging parts. Thecontroller is configured to carry out the first control based on thedisplacement calculated by the first displacement calculator. Thisprocess corresponds to the automatic alignment based on the imageobtained by the stereo photographing.

It is possible to apply other types of automatic alignment. For example,the imaging part is coaxially arranged with the optical system andobtains a moving image of the anterior eye part. This moving imagephotographing is, for example, acquisition of an infrared observationimage by using the retinal camera unit 2. Further, the informationobtaining part is configured to include an alignment optical system anda second displacement calculator. The alignment optical system isconfigured to project an alignment target on the anterior eye part. Thesecond displacement calculator is configured to calculate a displacementbetween the eye and the optical system by analyzing the moving image(for example, the infrared observation image) of the anterior eye parton which the alignment target is being projected. The controller isconfigured to carry out the first control (automatic alignment) based onthe displacement calculated by the second displacement calculator.

Any of the configurations explained in the embodiments below may beadded to any of the configurations in this embodiment.

Second Embodiment

When the alignment position is moved in the first embodiment (forexample, Step S28, Step S31), the destination may be represented to theuser. Thereby, the user can recognize the location to which thealignment position is moved. Further, there might be a case in which theuser wants to change the preset destination. In this embodiment,examples for satisfying such a request are explained.

For example, an ophthalmologic apparatus according to the presentembodiment includes the configuration similar to the first embodiment.The drawings of the first embodiment are referred to.

Upon receiving the operation to the “Search” button 1032 in the Step S27of FIG. 7A, the controller 210 displays information (destinationinformation) that indicates the predetermined destination of the opticalsystem over the front image of the fundus Ef on the display 241.Further, when the determination result “NO” is obtained in Step S30(that is, when the Auto-Z fails), the controller 210 displays similardestination information over the front image of the fundus Ef.

The destination of the optical system in Step S28 may be, as in thefirst embodiment, the position predetermined distance shifted from theinitial position (the position achieved by the automatic alignment ofStep S22) in a predetermined direction. This predetermined direction maybe the inferior direction or the nasal direction, and this predetermineddistance may be the maximum movement distance (for example, 0.7 mm) orless.

Moreover, the destination of the optical system in Step S31 may be, asin the first embodiment, the position predetermined distance shiftedfrom the initial position in a predetermined direction. Thispredetermined direction may be the opposite direction to the movementdirection in Step S28 (that is, the superior direction or the temporaldirection), and this predetermined distance may be same as the movementdistance in Step S28.

The display position of the destination information is determined basedon one or more preset factors such as the above predetermined directionand predetermined distance, the photographing magnification of the frontimage, the display magnification of the front image, etc. by, forexample, the controller 210.

The front image of the fundus Ef may be the same front image 3000 as thefirst embodiment, or other front images. Examples of other front imageinclude a front image obtained by OCT measurement (OCT front image). TheOCT front image is a cross sectional image (C-scan image) of a crosssection parallel to the xy-plane, and is formed from, for example,volume data or stack data obtained by three-dimensional scan.Alternatively, the OCT front image may be a projection image that isformed by projecting the voxel values of the volume data (or pixelvalues of the stack data) in the z-direction. In this case, it ispossible to project only a part of the volume data (or the stack data).Further, when an ophthalmologic apparatus capable of carrying out bothretina photographing and OCT measurement is used, an OCT front image canbe displayed over an retinal image obtained by retina photographing, andthis synthetic image (composed image) can be used as the front image.

Display modes of the destination information are explained. FIG. 12illustrates an example of the case in which the destination informationis displayed over the same front image 3000 as that in the firstembodiment. The destination information 1200 is a cruciform image;however, the shape thereof is arbitrary. Further, the display color ofthe destination information is arbitrary. Moreover, the destinationinformation may be blinked.

The user can confirm the destination of the optical system in the latermoving step by the destination information displayed on the front imageof the fundus Ef. When the destination can be accepted, the userperforms predetermined operation using the operation part 242. Uponreceiving this operation, the controller 210 moves the optical systemtoward this destination (Step S28, Step S31). It should be noted thatthe operation for accepting the destination is, for example, anoperation to a prescribed software key provided in a display screen (ora dialog box).

On the other hand, when the destination indicated by the destinationinformation cannot be accepted, the user can perform prescribedoperation using the operation part 242 to move the displayed destinationinformation to any desired position in the front image. The controller210 moves the optical system toward the position corresponding to thedestination information that has been moved by the user (Step S28, StepS31). It should be noted that the operation for moving the destinationinformation is, for example, an operation to a prescribed software keyprovided in a display screen, or a drag operation.

Effects of the Ophthalmologic Apparatus According to the PresentEmbodiment are Explained.

the ophthalmologic apparatus according to the present embodimentincludes a front-image obtaining part configured to obtain a front imageof the eye. The front-image obtaining part may include a configurationfor photographing a retina (for example, the retinal camera unit 2)and/or a configuration for obtaining an OCT image of an eye fundus (forexample, the OCT unit 100 and the image forming part 220). When it isdetermined that the information optically obtained by the optical systemis not appropriate, the controller (for example, the controller 210)displays information indicating a previously determined destination ofthe optical system (destination information) over the front image on adisplay means (for example, the display 241).

The displaying process of the destination information by the controlleris performed at an arbitrary timing after the above determination. As anexample thereof, the trigger of the displaying process may be theacquisition of the result of the above determination. For example, uponreceiving the determination result “NO” in Step S30, the controller maydisplay the destination information. As another example, the trigger ofthe displaying process may be the execution of a prescribed operation bythe user after the acquisition of the result of the above determination.For example, upon receiving the selection of “Search” in Step S27, thecontroller may display the destination information.

According to such an embodiment, it is possible to represent thedestination of the optical system (that is, the destination of thealignment position) to the user.

In this embodiment, the controller may be configured, when the displayposition of the destination information is changed by using an operatingmeans (for example, the operation part 242), to carry out control of themoving mechanism (for example, the optical system driver 2A) such thatthe optical system is moved to the destination after this change.According to this configuration, the user can move the alignmentposition to a desired position.

Third Embodiment

In the second embodiment, the case in which the destination of theoptical system (the destination of the alignment position) is determinedin advance is explained. In contrast, this embodiment describes examplesapplicable the case in which the destination of the optical system isnot determined in advance. The configuration according to thisembodiment can be applied to the ophthalmologic apparatuses of the firstand the second embodiments.

An ophthalmologic apparatus according to this embodiment includes thesimilar configuration to that of the first embodiment, for example. Thedrawings of the first embodiment are referred to.

Upon receiving the operation to the “Search” button 1032 in the Step S27of FIG. 7A, the controller 210 displays information (destinationdesignating information) for designating the destination of the opticalsystem over the front image of the fundus Ef on the display 241.Further, when the determination result “NO” is obtained in Step S30(that is, when the Auto-Z fails), the controller 210 displays similardestination designating information over the front image of the fundusEf.

The destination designating information may be an image similar to thedestination information 1200 in the second embodiment. Further, theposition (initial display position) in which the destination designatinginformation is initially displayed is arbitrary, and it is, for example,the center position of the front image. The user can perform aprescribed operation using the operation part 242 to move the displayposition of the destination designating information to a desiredposition. This operation is an operation to a software key provided in adisplay screen, or a drag operation. Thereby, the destination of thealignment position is designated. The controller 210 controls theoptical system driver 2A so as to move the optical system to thedesignated position.

Instead of displaying the destination designating information at theinitial display position, the controller 210 may display informationurging the user to designate the destination of the alignment position(for example, a dialog box) on the front image. The user performs aprescribed operation using the operation part 242 to designate a desiredposition in the front image. This operation is, for example, a clickoperation. The controller 210 may display information (an image)indicating the designated position. The user may perform, for example, adrag operation to move the display position of this image. Thereby, thedestination is adjusted. The controller 210 controls the optical systemdriver 2A to move the optical system to the destination designated bythe user.

Effects of the ophthalmologic apparatus according to the presentembodiment are explained.

the ophthalmologic apparatus according to the present embodimentincludes a front-image obtaining part configured to obtain a front imageof the eye. The front-image obtaining part may include a configurationfor photographing a retina (the retinal camera unit 2) and/or aconfiguration for obtaining an OCT image of an eye fundus (the OCT unit100 and the image forming part 220). The controller (the controller 210)displays the obtained front image on a display means (the display 241).Further, When it is determined that the information optically obtainedby the optical system after the first control and also when a positionin the front image displayed on the display means is designated by usingan operating means, the controller carries out control of the movingmechanism (the optical system driver 2A) such that the optical system ismoved to the designated position.

According to such an embodiment, it is possible to move the alignmentposition to any position desired by the user.

Fourth Embodiment

This embodiment describes examples of representing a region of interestof an eye for facilitating the movement of the alignment position. Theregion of interest corresponds to a factor that's disturbs light such asan opaque portion. A configuration according to this embodiment isapplicable to the ophthalmologic apparatuses of the second and the thirdembodiments.

An ophthalmologic apparatus according to this embodiment includesconfigurations similar to that in the first embodiment, for example. Thedrawings of the first embodiment are referred to.

An ophthalmologic apparatus according to this embodiment includes afunction for obtaining information indicating a region of interest inthe eye E (a region-of-interest obtaining part).

The first example of the region-of-interest obtaining part includes theretinal camera unit 2 and the image processor 230. The retinal cameraunit 2 photographs the eye E. A method for clearly depicting the regionof interest may be applied to this photographing. For example, when theregion of interest is an opaque portion, the red reflex imaging can beapplied. The red reflex imaging is a method of depicting an opaqueportion with high contrast by using the red-color reflection ofillumination light from the fundus Ef as back light.

The image processor 230 analyzes an image (eye image) of the eye Eobtained by the retinal camera unit 2 to specify the image region(interest image region) corresponding to the region of interest. Thecontroller 210 stores information indicating the interest image regionspecified in the storage 212. This information may include any of thefollowings: positional information (e.g. coordinates) of the interestimage region in the eye image; relative positional informationindicating the position of the interest image region relative to theimage region corresponding to a prescribed site of the eye E (e.g.pupil, iris, vesica, optic papilla, macula, blood vessel, disease part,etc.); the eye image itself.

The controller 210 reads out the information indicating the interestimage region from the storage 212 to display the front image of the eyeE (for example, the front image 300 of FIG. 8D). further, the controller210 displays the information indicating the area of the region ofinterest (interest area information) over this front image based on theinformation read out. The interest area information is, for example, animage indicating the outline of the region of interest (interest imageregion).

When the eye image is stored in the storage 212, the process fordisplaying the interest area information may include image matchingbetween the eye image and the front image. The controller 210 maydetermine the display position of the interest area information relativeto the front image based on the result of the image matching.

When the relative positional information of the interest image regionrelative to the image region corresponding to a prescribed site of theeye E is stored in the storage 212, the process for displaying theinterest area information may include a process for specifying the imageregion in the front image corresponding to the prescribed site of theeye E. The controller 210 may determine the display position of theinterest area information relative to the front image based on thespecified image region and the relative positional information.

When the positional information of the interest image region in the eyeimage is stored in the storage 212, the controller 210 may display theinterest area information so as to match the image region indicated bythis positional information (coordinates) in the front image.

It is possible to apply the same fixation position for both theacquisition of the eye image and the acquisition of the front image. Onthe other hand, in the case in which the fixation positions aredifferent, the apparatus may convert the displacement of the fixationpositions into the displacement in an image, and change the displayposition of the interest area information based on this imagedisplacement. Further, the photographing magnifications of the eye imageand the front image may be the same, and/or the display magnificationsof the eye image and the front image may be the same. When thephotographing magnifications and/or the display magnifications are/isdifferent, the apparatus can adjust the display size of the interestarea information based on the difference(s) in the magnification(s).

The second example of the region-of-interest obtaining part includes aconfiguration for inputting data from external devices to theophthalmologic apparatus (data inputting part). The data inputting partmay include a communication interface and/or a drive device. Thecommunication interface is provided for data communication to externaldevices via a network. In this embodiment, the communication interfacereceives an eye image and/or information indicating interest imageregion transmitted from an external device. The drive device is providedfor reading data recorded in media. In this embodiment, the drive devicereads an eye image and/or information indicating interest image regionrecorded in a medium.

The eye image and/or information indicating interest image region inputby the communication interface is stored in the storage 212 by thecontroller 210 the controller 210 displays the interest area informationover the front image of the eye E based on information indicating theinterest image region etc. stored on the storage 212. This displayprocess may be carried out in the way similar to the first example.

Effects of the ophthalmologic apparatus according to the presentembodiment are explained.

The ophthalmologic apparatus according to the present embodimentincludes a region-of-interest obtaining part configured to obtaininformation indicating a region of interest in the eye. Theregion-of-interest obtaining part may be configured to obtain theinformation indicating the region of interest based on an image obtainedby red reflex imaging previously performed to the eye. Further, thecontroller is configured to display the information indicating theregion of interest obtained over the front image of the eye.

According to such configurations, it is possible to represent theposition of the region of interest corresponding to an opaque portion inthe eye etc. The user may set an alignment position so as to avoid theregion of interest.

It is also possible to configure to automatically set the alignmentposition based on the information indicating the region of interestobtained by the region-of-interest obtaining part. In this case, thecontroller may control, based on the information indicating the regionof interest, the moving mechanism such that the optical system is movedto a position in which the region of interest does not exist. Thedestination of the optical system may be the position closest to theinitial position (for example, the center of the pupil) in the region inwhich the region of interest does not exist. Here, it is possible to setthe destination so as to be away from the outline of the region ofinterest by a prescribed distance. This prescribed distance may be setin advance by taking the beam diameter of signal light intoconsideration.

Fifth Embodiment

This embodiment describes examples for automatically searching asuitable alignment position. The configuration of this embodiment isapplicable to the ophthalmologic apparatuses of the first to the fourthembodiments.

An ophthalmologic apparatus according to this embodiment includesconfigurations similar to that in the first embodiment, for example. Thedrawings of the first embodiment are referred to.

The controller 210 interlockingly carries out control of causing theoptical system (the retinal camera unit 2 and/or the OCT unit 100) torepeatedly perform acquisition of the optical information (informationacquisition control), and control of causing the moving mechanism (theoptical system driver 2A) to stepwise move the optical system (movementcontrol). The information acquisition control and the movement controlare alternately executed, for example.

The information acquisition control may include Auto-Z. In the movementcontrol, control of moving the optical system by a prescribeddisplacement (displacement direction and displacement amount) isrepeatedly performed. The displacement direction is, for example,firstly the inferior (or nasal) direction and secondly the superior (ortemporal) direction. The displacement amount is arbitrarily set.

The controller 210 determines whether this interlocking control iscontinued or ended based on information successively obtained by theoptical system during this interlocking control. For example, at eachposition of the optical system that is stepwise moved (that is, at eachstep of the gradual movement of the examination optical system), thedetermination process of the success/failure of the Auto-Z is included.This determination process is carried out in the way similar to Step S25of FIG. 7A, for example. When the Auto-Z fails, the controller 210continues the above interlocking control. On the other hand, When theAuto-Z succeeds; the controller 210 terminates the above interlockingcontrol. In other words, the controller 210 continues the aboveinterlocking control until the Auto-Z succeeds. Thereby, the opticalsystem is located in a suitable alignment position.

When a preset series of movement controls is completed (for example,when the examination optical system is moved in the superior directionby a prescribed distance after movement in the inferior direction by aprescribed distance), the controller 210 may terminate the aboveinterlocking control. In this case, the controller 210 may displayinformation indicating the failure to search the alignment position onthe display 241. Further, the controller 241 may display a software keyfor the user to select a subsequent process on the display 241. Theoptions may include, for example, any of re-execution of the samesearching process, execution of a searching process including movementcontrol of different type, and execution of manual alignment.

Effects of the ophthalmologic apparatus according to the presentembodiment are explained.

In the second control (the movement control of the optical systemexecuted after automatic alignment), the controller (for example, thecontroller 210, the image forming part 200 and image processor 230) ofthe ophthalmologic apparatus according to the present embodimentinterlockingly carries out control of causing the optical system torepeatedly perform acquisition of the optical information and control ofcausing the moving mechanism (the optical system driver 2A) to stepwisemove the optical system. Further, the controller determines whether thisinterlocking control is continued or ended based on informationsuccessively obtained by the optical system during this interlockingcontrol.

According to such an ophthalmologic apparatus, it is possible toautomatically locate the optical system in the position in which theexamination can be preferably carried out.

Modified Example

The embodiments described above are merely examples. One who intends toimplement the present invention may arbitrarily modify (omission,replacement, addition, etc.) within the scope of the invention.

In the above embodiments, the difference in optical path length betweenthe optical path of the signal light LS and the optical path of thereference light LR is changed by changing the position of theoptical-path-length changing part 41; however the method for changingthe difference in optical path length is not limited to this. Forexample, it is possible to change the difference in optical path lengthby providing a reflection mirror (reference mirror) in the optical pathof the reference light, and moving this reference mirror along thepropagation direction of the reference light to change the optical pathlength of the reference light. Moreover, it is possible to change theoptical path length of the signal light LS by moving the retinal cameraunit 2 and/or the OCT unit 100 relative to the eye E, thereby changingthe difference in optical path length. Moreover, particularly if theobject being measured is not a region of a living body, it is possibleto change the difference in optical path length by moving the objectbeing measured in the depth direction (z-direction).

Computer programs for realizing the above embodiments can be stored inany kind of recording medium that can be read by a computer. As thisrecording medium, for example, a semiconductor memory, an optical disk,a magneto-optic disk (CD-ROM, DVD-RAM, DVD-ROM, MO, and so on), and amagnetic storage (a hard disk, a Floppy Disk™, ZIP, and so on) can beused.

What is claims is:
 1. An ophthalmologic apparatus comprising: anexamination part configured to include an optical system for opticallyexamining an eye; a moving mechanism configured to move the opticalsystem; an information obtaining part configured to obtain informationfor carrying out position matching of the optical system to the eye; acontroller configured to carry out first control for the movingmechanism based on the information obtained by the information obtainingpart to move the optical system, determine whether information opticallyobtained by the optical system after the first control is appropriate tothe examination or not, and when it is determined that this informationis not appropriate, carry out second control for the moving mechanism inresponse to a prescribed trigger to move the optical system.
 2. Theophthalmologic apparatus of claim 1, wherein the controller isconfigured to determine whether information optically obtained by theoptical system after the second control is appropriate to theexamination or not, and when it is determined that this information isnot appropriate, carry out third control for the moving mechanism tomove the optical system.
 3. The ophthalmologic apparatus of claim 2,wherein the controller is configured to move the optical system in afirst direction by the second control, and move the optical system in asecond direction that is the opposite direction to the first directionby the third control.
 4. The ophthalmologic apparatus of claim 3,wherein the controller is configured to move, by the second control, theoptical system to the position that is prescribed distance away in thefirst direction from the position after the movement by the firstcontrol, and move, by the third control, the optical system to theposition that is the prescribed distance away in the second directionfrom the position after the movement by the first control.
 5. Theophthalmologic apparatus of claim 3, wherein the first direction is adownward direction or a sagittal line direction.
 6. The ophthalmologicapparatus of claim 1, wherein the optical system is configured toirradiate light from a light source onto an eye fundus, and detectreturned light of this light from the eye fundus, and the controller isconfigured to perform the determination based on the detection result ofthe returned light.
 7. The ophthalmologic apparatus of claim 6, whereinthe optical system is configured to split light from the light sourceinto signal light and reference light, scan the eye fundus with thesignal light, and detect interference light obtained by composingreturned light of the signal light from the eye fundus and the referencelight, the examination part is configured to include a cross sectionalimage forming part configured to form a cross sectional image of the eyefundus based on the detection result of the interference light by theoptical system, and the controller is configured to carry out thedetermination based on the detection result of the interference light orthe cross sectional image.
 8. The ophthalmologic apparatus of claim 7,wherein the optical system is configured to include anoptical-path-length changing part configured for relatively changingoptical path length of the signal light and optical path length of thereference light the controller is configured to, in the determination,while controlling the optical system in such a way as to repeatedly scanthe same portion of the eye fundus, control the optical-path-lengthchanging part such that the eye fundus is depicted in a prescribed areain a frame based on detection results of the interference light or crosssectional images repeatedly obtained by this control, and determine thatthe information optically obtained by the optical system is notappropriate when the eye fundus is not depicted in the prescribed area.9. The ophthalmologic apparatus of claim 1, wherein the controller isconfigured to display an object including a first operating element on adisplay means when it is determined that the information opticallyobtained by the optical system after the first control is notappropriate, and the prescribed trigger is operation to the firstoperating element performed using an operating means.
 10. Theophthalmologic apparatus of claim 9, wherein the object includes asecond operating element, and the controller is configured to carry outacquisition of information by the optical system again when operation tothe second operating element is performed by using the operating means.11. The ophthalmologic apparatus of claim 1, further comprising afront-image obtaining part configured to obtain a front image of theeye, wherein the controller is configured to display, on a displaymeans, information indicating a previously determined destination of theoptical system over the front image when it is determined that theinformation optically obtained by the optical system is not appropriate.12. The ophthalmologic apparatus of claim 11, wherein the controller isconfigured to, when the display position of the information indicatingthe destination is changed by using an operating means, carry outcontrol of the moving mechanism such that the optical system is moved tothe destination after this change.
 13. The ophthalmologic apparatus ofclaim 1, further comprising a front-image obtaining part configured toobtain a front image of the eye, wherein the controller is configured todisplay the front image on a display means, and when it is determinedthat the information optically obtained by the optical system after thefirst control is not appropriate and also when a position in the frontimage displayed on the display means is designated by using an operatingmeans, carry out control of the moving mechanism such that the opticalsystem is moved to the designated position.
 14. The ophthalmologicapparatus of claim 11 or 13, further comprising a region-of-interestobtaining part configured to obtain information indicating a region ofinterest in the eye, wherein the controller is configured to display theinformation indicating the region of interest over the front image. 15.The ophthalmologic apparatus of claim 14, wherein the region-of-interestobtaining part is configured to obtain the information indicating theregion of interest based on an image obtained by red reflex imagingpreviously performed to the eye.
 16. The ophthalmologic apparatus ofclaim 1, wherein the information obtaining part is configured to includeone or more imaging part configured to obtain a moving image of ananterior eye part of the eye, the controller is configured to carry outthe first control based on the moving image.
 17. The ophthalmologicapparatus of claim 16, wherein the information obtaining part isconfigured to include two imaging parts non-coaxially arranged to theoptical system, and a first displacement calculator configured tocalculate a displacement between the eye and the optical system byanalyzing two images substantially simultaneously obtained by the twoimaging parts, and the controller is configured to carry out the firstcontrol based on the displacement calculated by the first displacementcalculator.
 18. The ophthalmologic apparatus of claim 16, wherein theimaging part is coaxially arranged with the optical system and obtains amoving image of the anterior eye part, and the information obtainingpart is configured to include an alignment optical system configured toproject an alignment target on the anterior eye part, and a seconddisplacement calculator configured to calculate a displacement betweenthe eye and the optical system by analyzing the moving image of theanterior eye part on which the alignment target is being projected, andthe controller is configured to carry out the first control based on thedisplacement calculated by the second displacement calculator.
 19. Theophthalmologic apparatus of claim 1, wherein the controller isconfigured to, in the second control, interlockingly carry out controlof causing the optical system to repeatedly perform acquisition of theoptical information and control of causing the moving mechanism tostepwise move the optical system, and determine whether thisinterlocking control is continued or ended based on informationsuccessively obtained by the optical system during this interlockingcontrol.